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WO1999008614A1 - Dispositifs, procedes et systemes non effractifs permettant de resserrer des tissus - Google Patents

Dispositifs, procedes et systemes non effractifs permettant de resserrer des tissus Download PDF

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Publication number
WO1999008614A1
WO1999008614A1 PCT/US1998/016754 US9816754W WO9908614A1 WO 1999008614 A1 WO1999008614 A1 WO 1999008614A1 US 9816754 W US9816754 W US 9816754W WO 9908614 A1 WO9908614 A1 WO 9908614A1
Authority
WO
WIPO (PCT)
Prior art keywords
tissue
electrode
probe
heating
target tissue
Prior art date
Application number
PCT/US1998/016754
Other languages
English (en)
Inventor
Frank Ingle
Garry L. Carter
Robert J. Laird
John P. Claude
Paul Do
Brian J. Mosel
Original Assignee
Surx, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from US08/910,369 external-priority patent/US6035238A/en
Priority claimed from US08/910,371 external-priority patent/US6081749A/en
Priority claimed from US08/910,775 external-priority patent/US6480746B1/en
Application filed by Surx, Inc. filed Critical Surx, Inc.
Priority to CA002300152A priority Critical patent/CA2300152A1/fr
Priority to JP2000509360A priority patent/JP2001514921A/ja
Priority to DE69834644T priority patent/DE69834644T2/de
Priority to AU91038/98A priority patent/AU732188B2/en
Priority to EP98943191A priority patent/EP1003432B1/fr
Publication of WO1999008614A1 publication Critical patent/WO1999008614A1/fr

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14—Probes or electrodes therefor
    • A61B18/1482—Probes or electrodes therefor having a long rigid shaft for accessing the inner body transcutaneously in minimal invasive surgery, e.g. laparoscopy
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14—Probes or electrodes therefor
    • A61B18/1485—Probes or electrodes therefor having a short rigid shaft for accessing the inner body through natural openings
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—Details
    • A61N1/04—Electrodes
    • A61N1/06—Electrodes for high-frequency therapy
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/40—Applying electric fields by inductive or capacitive coupling ; Applying radio-frequency signals
    • A61N1/403—Applying electric fields by inductive or capacitive coupling ; Applying radio-frequency signals for thermotherapy, e.g. hyperthermia
    • A—HUMAN NECESSITIES
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    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14—Probes or electrodes therefor
    • A—HUMAN NECESSITIES
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    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/1815—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using microwaves
    • A—HUMAN NECESSITIES
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    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
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    • A61B2017/003—Steerable
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    • A61B2018/00005—Cooling or heating of the probe or tissue immediately surrounding the probe
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    • A61B2018/00011—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids
    • A61B2018/00023—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids closed, i.e. without wound contact by the fluid
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    • A61B2018/00083—Electrical conductivity low, i.e. electrically insulating
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    • A61B2018/00505—Urinary tract
    • A61B2018/00517—Urinary bladder or urethra
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Definitions

  • Urinary incontinence arises in both women and men with varying degrees of severity, and from different causes.
  • Excessive length of the pelvic support tissues can lead to a variety of ailments including, for example, cystocele, in which a portion of the bladder protrudes into the vagina.
  • Excessive length of the tissues supporting the breast may cause the breasts to sag.
  • Many hernias are the result of a strained ? torn, and/or distended containing tissue, which allows some other tissue or organ to protrude beyond its contained position.
  • Cosmetic surgeries are also often performed to decrease the length of support tissues. For example, abdominoplasty (often called a "tummy tuck") is often performed to decrease the circumference of the abdominal wall . The distortion of these support tissues may be due to strain, advanced age, congenital predisposition, or the like.
  • fascia, tendons, and the other support tissues of the body It would be particularly desirable to provide improved noninvasive or minimally invasive therapies for these support tissues, especially for the treatment of urinary incontinence in men and women. It would further be desirable to provide treatment methods which made use of the existing support structures of the body, rather than depending on the specific length of an artificial support structure.
  • U.S. Patent No. 5,423,811 describes a method for RF ablation using a cooled electrode.
  • U.S. Patent Nos. 5,458,596 and 5,569,242 describe methods and an apparatus for controlled contraction of soft tissue.
  • An RF apparatus for controlled depth ablation of soft tissue is described in U.S. Patent 5,514,130.
  • the plate electrode comprises an electrode array which includes several discrete electrode surface segments so that the current flux can be varied to selectively target and evenly heat the fascia.
  • the tissue is heated between a pair of parallel cooled electrode surfaces, the parallel surfaces optionally being planar, cylindrical, spherical, or the like.
  • the tissue may be treated with a bipolar probe, particularly after pre-cooling the intermediate tissue to selectively vary tissue impedance and thereby direct the heating current through the target tissue .
  • the present invention provides a probe for therapeutically heating a target tissue of a patient body through an intermediate tissue.
  • the probe comprises an electrode with an electrode surface which is engagable against the intermediate tissue.
  • the electrode surface is substantially flat, and a cooling system is coupled to the electrode. The cooling system allows the electrode surface to cool the engaged intermediate tissue while an electrical current flux from the electrode surface therapeutically heats the target tissue.
  • the electrode surface will generally be sufficiently flat to direct the current flux through the cooled intermediate tissue and into the target tissue while the cooling system maintains the intermediate tissue at or below a maximum safe tissue temperature.
  • heating may be provided between a pair of electrode surfaces, the electrode surfaces typically being separated by a distance from about 1/3 to about 5.0 times the least width of the electrodes, preferably being separated by a distance from about 1/2 to about 2.0 times the least electrode width.
  • a temperature sensor will monitor the temperature of the target tissue or the intermediate tissue.
  • a control system will often selectively energize the electrode and/or cooling system in response to the monitored temperature .
  • the present invention provides a probe for applying energy to fascia from within the vagina of a patient body.
  • the fascia is separated from the vagina by a vaginal wall.
  • the probe comprises a probe body having a proximal end and a distal end, the probe having a length and a cross-section selected to permit introduction into the vagina.
  • An energy transmitting element is mounted to the probe body.
  • the transmitting element is capable of transmitting sufficient heating energy through the vaginal wall to heat and contract the fascia.
  • a cooling system is disposed adjacent to the transmitting element. The cooling system is capable of maintaining the vaginal wall adjacent the probe below a maximum safe temperature when the fascia is heated by the transmitting element.
  • the present invention also provides a method for shrinking a target collagenated tissue within a patient body through an intermediate tissue.
  • the method comprises directing energy from a probe, through the intermediate tissue, and into the target tissue.
  • the energy heats the target tissue so that the target tissue contracts.
  • the intermediate tissue is cooled with the probe to avoid injuring the intermediate tissue when the target tissue is heated by the probe .
  • the present invention provides a method for directing energy into a target tissue of a patient body through an intermediate tissue.
  • the method comprises electrically coupling a first electrode to the patient body.
  • a second electrode is electrically coupled to the intermediate tissue, the second electrode being mounted on a probe.
  • the intermediate tissue is cooled by the probe, and an electrical potential is applied between the first and second electrodes.
  • An electrode surface of the second electrode is sufficiently large and flat to provide a current flux that extends through the cooled intermediate tissue so that the current flux heats the target tissue.
  • the present invention provides a method for therapeutically heating a target zone of a tissue within a patient body.
  • the method comprises engaging a tissue adjacent to the target zone with a probe.
  • the adjacent tissue is pre-cooled with the probe, and the target zone is heated by directing energy from the probe, through the pre-cooled adjacent tissue, and into the target zone.
  • the present invention provides a kit for shrinking a target collagenated tissue within a patient body through an intermediate tissue.
  • the kit comprises a probe having an energy transmitting element adapted to direct an energy flux through the intermediate tissue and into the target tissue.
  • a cooling system is adjacent to the transmitting element to cool the intermediate tissue.
  • the kit also includes instructions for operating the probe. The instructions comprise the steps of directing energy from the energy transmitting element of the probe, through the intermediate tissue, and into the target tissue so as to heat and shrink the target tissue.
  • the intermediate tissue is cooled with the cooling system of the probe to avoid injuring the intermediate tissue.
  • the present invention further provides a method for teaching.
  • the method comprises demonstrating cooling of a surface with a probe. Directing of energy from the probe is also demonstrated, the energy being directed through the surface and into the underlying structure to effect shrinkage of the structure.
  • the present invention provides a method for therapeutically heating a target zone of a patient body.
  • the target zone is disposed within a tissue between first and second tissue surfaces.
  • the method comprises engaging a first electrode surface against the first tissue surface.
  • a second electrode surface is aligned substantially parallel with the first electrode surface and against the second tissue surface.
  • An electrical potential is applied between the first and second electrodes so as to produce an electrical current flux which heats the target zone.
  • At least one of the first and second tissue surfaces is cooled by the engaged electrode.
  • the method comprises engaging a probe against the tissue.
  • the probe has a plurality of electrode surface segments, and the tissue is cooled adjacent the probe by the electrode surface segments.
  • An electrical current flux is directed from the electrode surface segments, through the cooled tissue, and into the target zone by selectively energizing the electrode surface segments so that the current flux substantially evenly heats the target zone.
  • tissue contraction energy will preferably be in the form of a radiofrequency (RF) electrical current applied through an electrolytic solution.
  • RF radiofrequency
  • Such cooling may be enhanced by circulating chilled conductive solution through the bladder, optimizing the electrical properties of the solution to minimize heat generated within the solution, and the like.
  • the RF energy is transmitted between the electrolyte/bladder wall interface and a cooled, substantially flat electrode of a vaginal probe so as to shrink the endopelvic fascia therebetween and thereby inhibit incontinence.
  • a method for heating a target tissue within a patient body heats tissue separated from a body cavity by an intermediate tissue.
  • the method comprises introducing a conductive fluid into the cavity.
  • An electrical current is passed from the conductive fluid, through the intermediate tissue, and into the target tissue to effect heating of the target tissue.
  • the intermediate tissue is cooled by the conductive fluid.
  • the conductive fluid will generally comprise an electrolytic solution such as saline, and the saline will preferably be chilled.
  • an intermediate collagenated tissue therebetween can be selectively raised above about 60 «C, thereby inducing shrinkage.
  • the invention provides a method for shrinking a target tissue within a patient body.
  • the target tissue is separated from a body cavity by an intermediate tissue.
  • the method comprises introducing a conductive fluid and an insulating fluid into the cavity. These fluids are positioned within the cavity by orienting the patient.
  • the conductive and insulating fluids will have differing densities, and the patient will be oriented so that the conductive fluid is disposed adjacent the target tissue, while the insulating fluid is disposed away from the target tissue.
  • the target tissue can then be heated by passing an electrical current from the conductive fluid, through the - intermediate tissue, and into the target tissue.
  • the intermediate tissue can also be cooled by the conductive fluid.
  • the conductive fluid will often comprise an electrolytic liquid such as saline, while the insulating fluid will typically comprise a gas such as air, carbon dioxide, or the like.
  • the present invention provides a method for treating urinary incontinence.
  • the method comprises introducing a fluid into the bladder, and transmitting electrical current from the fluid, through the bladder wall, and into a pelvic support tissue so that the current heats and shrinks the pelvic support tissue and inhibits urinary incontinence.
  • the bladder wall is cooled with the conductive fluid.
  • the present invention provides a system for shrinking a pelvic support tissue of a patient body.
  • the pelvic support tissue is separated from a urinary bladder by a bladder wall.
  • the system comprises a first probe having a proximal end and a distal end adapted for transurethral insertion into the bladder.
  • a first electrode is disposed near the distal end, as is a fluid in-flow port.
  • the present invention provides a system for shrinking a pelvic support tissue of a patient body.
  • the pelvic support tissue is separated from a urinary bladder by a bladder wall.
  • the system comprises a first probe having a proximal end, a distal end adapted for transurethral insertion into the bladder, and a first electrode near the distal end.
  • a second probe has a proximal end, a distal end adapted for insertion into the vagina, and a second electrode near the distal end.
  • a power source is coupled to the first and second electrodes to heat and shrink the pelvic support tissue.
  • the first probe will also include a tordial balloon or other member for sealing around the circumference of the probe, thereby allowing saline or some other conductive fluid to be captured within the bladder.
  • in-flow and out-flow ports distal of the balloon may allow circulation of chilled saline or the like, enhancing the direct cooling of the bladder wall.
  • One or more gas ports may also be provided distal of the balloon for introducing and/or controlling a volume of air, C0 2 or some other insulating gas, or such gasses may alternatively pass through the conductive fluid ports.
  • such a structure can provide both selective electrical conduction and cooling over a large, controlled surface of the bladder wall with very little mechanical complexity or trauma.
  • the tissue contraction energy of the present invention can be applied as intermittent pulses of radiofrequency (RF) electrical current transmitted between cooled electrodes.
  • the electrodes will ideally be large, relatively flat plates having rounded edges, but may alternatively comprise a curved conductive surface of an inflatable balloon, or the like. These electrodes will preferably be oriented toward each other, and will generally be actively cooled while the electrodes are energized by a- RF potential, and between RF pulses. Cooling will preferably also be provided both before and after the heating cycles, and needle mounted temperature sensors will ideally provide direct feedback of the tissue temperature so that selected treatment zone is heated to about 60nC or more, while heating of the tissues adjacent the electrodes is limited to about 45 «C or less.
  • the present invention provides a method for heating and/or shrinking a target tissue within a patient body.
  • the target tissue is separated from a tissue surface by an intermediate tissue.
  • the method comprises coupling an electrode of a probe to the tissue surface and cooling the intermediate tissue with the probe.
  • the electrode is intermittently energized to heat, and preferably to shrink, the target tissue through the cooled intermediate tissue.
  • current is driven through the electrode for between about 10 and 50% of a heating session.
  • the electrode may be energized for 15 sees, and turned off for 15 sees, repeatedly during a heating session so that current is driven from the electrode for about 50% of the duty cycle.
  • the invention provides a system for shrinking a target tissue of a patient body.
  • the system comprises a probe having a first electrode for electrically coupling the probe to the tissue surface.
  • a second electrode can be coupled to the patient body, and a controller is coupled to the first and second electrodes.
  • the controller is adapted to intermittently energize the electrodes with an RF current so that the electrodes heat and shrink the target tissue, often while minimizing collateral damage to tissues surrounding the target tissue.
  • the target tissue is separated from a tissue surface by an intermediate tissue.
  • a cooling system may be disposed adjacent the electrode, so that the cooling system can maintain the intermediate tissue below a maximum safe temperature. Generally, the cooling system will cool both the first electrode and the intermediate tissue engaged by the electrode surface.
  • the energy to heat and selectively shrink the target collagenated support tissues will preferably be applied by conducting radiofrequency (RF) electrical current through tissue disposed between large, cooled plate electrodes.
  • RF radiofrequency
  • These electrodes will preferably be sufficiently parallel to each other and in alignment so as to direct the current flux evenly throughout a target region of the target tissue.
  • the electrodes will generally be mechanically coupled to each other, ideally using a clamp structure which allows the target tissue to be compressed between the electrode surfaces. Compressing the tissues can enhance the uniformity of the heating, particularly when the tissue is compressed between the electrode surfaces so that the surfaces are separated by less than their widths. Cooling of the electrodes can limit heating of tissues adjacent the electrode surfaces to about 45 «C or less, even when the treatment zone between the electrodes is heated to about 60nC or more so as to effect shrinkage .
  • the present invention provides a device for therapeutically heating tissue.
  • the device comprises a first electrode having an electrode surface.
  • a cooling system is thermally coupled to the first electrode.
  • a second electrode is mechanically coupled to the first electrode.
  • the second electrode has an electrode surface oriented toward the first electrode surface.
  • a clamp structure couples the electrodes and allows the tissues to be compressed between parallel electrode surfaces.
  • the clamp structure will often be adapted to maintain the electrode surfaces in alignment to each other, and also to maintain the electrode surfaces sufficiently parallel so as to direct an even electrical current flux through a target region of the clamped tissue.
  • At least one of the electrodes will preferably be mounted on a probe adapted for insertion into a patient body.
  • the probe will ideally be adapted for noninvasive insertion into a body cavity through a body orifice.
  • the clamp structure will preferably vary a separation distance between electrodes mounted on two such probes, and a temperature sensor will - ideally be extendable into the target tissue to provide feedback on the heating process.
  • the temperature sensor can be mounted on a needle which is retractably extendable from adjacent one of the electrodes toward the other, or the needle may protrude permanently so as to extend into the target tissue as the electrode surfaces are clamped together.
  • the present invention provides a method for selectively shrinking a target tissue. The method comprises clamping a target tissue between a plurality of electrode surfaces. The clamped target tissue is heated by transmitting a current flux between the electrode surfaces. At least one of the electrode surfaces is cooled to limit heating of intermediate tissue disposed between the at least one electrode and the target tissue.
  • the energy can be in the form of focused ultrasound energy.
  • Such ultrasound energy may be safely transmitted through an intermediate tissue at lower power densities so as to avoid and/or minimize collateral damage.
  • the power densities at the target region will be sufficiently high to increase the temperature of the target tissue.
  • the target tissue will be raised to a temperature of about 60nC or more, while the intermediate tissue remains at or below a maximum safe temperature of about 45 «C.
  • a cooling system may actively cool the intermediate tissue.
  • the present invention provides a system for heating a target tissue.
  • the system comprises a probe having an ultrasound transmitter for focusing ultrasound energy through the intermediate tissue so as to heat the target tissue.
  • a temperature sensor is coupled to the probe and exposed to at least one of the intermediate tissue and the target tissue for sensing a tissue temperature.
  • a controller is coupled to the probe. The controller will generally be adapted to direct the ultrasound energy from the transmitter into the target tissue so as to heat the target tissue to about 60flC or more. The controller will typically limit a temperature of the intermediate tissue to about 45nC or less.
  • the present invention provides a method for selectively heating a predetermined target tissue.
  • the target tissue is disposed adjacent another tissue, and the method comprises generating a temperature differential between the adjacent tissue and the target tissue.
  • the target tissue is heated by conducting a heating electrical current into the target tissue after generating the temperature differential .
  • the heating current is conducted so that the temperature differential urges the heating current from the adjacent tissue into the target tissue.
  • Figs. 2A-2F schematically illustrate structures and methods for selectively energizing the electrode surface segments of the large, flat electrode arrays of the system of Fig. 1 to tailor the current flux throughout a target zone.
  • Fig. 4 is a cut-away view illustrating pelvic support structures which can be targeted for non- invasive selective contraction using the methods of the present invention.
  • Figs. 4A-4C illustrate contraction and reinforcing of the pelvic support tissues of Fig. 4 as a therapies for female urinary incontinence.
  • Fig. 7 illustrates an alternative bladder electrode structure for use in the method of Fig. 6.
  • Fig. 11 schematically illustrates an alternative method for selectively shrinking endopelvic fascia using a vaginal probe having a cooled electrode array and a return electrode.
  • Figs. 18A-C illustrates a clamping structure having a transvaginal probe and a transrectal probe, in which each of the probes includes an electrode surface, and in which the probes are mechanically coupled by a clamping structure for compressing the targeted endopelvic fascia (together with . intermediate tissues) between a pair of opposed, cooled plate electrodes.
  • Treatment of other conditions may be effected by selective shrinking of a wide variety of other tissues, including (but not limited to) the diaphragm, the abdominal wall, the breast supporting ligaments, the fascia and ligaments of the joints, the collagenated tissues of the skin, and the like.
  • other tissues including (but not limited to) the diaphragm, the abdominal wall, the breast supporting ligaments, the fascia and ligaments of the joints, the collagenated tissues of the skin, and the like.
  • Related devices, methods, and system are also described in co-pending U.S. Patent Application Serial No. 08/910,370, filed August 13, 1997.
  • the temperature of the target tissue structure will generally be raised to a value in the range from about 60nC to 11OnC, often being in the range from about 60 «C to 80nC, and will generally effect a shrinkage of the target tissue in at least one dimension of between about 20 and 50 percent.
  • heating energy will be applied for a period of from 30 seconds to 5 minutes. These heating times will vary with separation between the parallel plate electrodes-, with a heat time of about 5 minutes often being appropriate for an electrode separation of about 4 cm. Shorter heat times may be used with smaller electrode separation distances.
  • the total amount of energy delivered will depend in part on which tissue structure is being treated, how much tissue is disposed between the target tissue and the heating element, and the specific temperature and time selected for the protocol.
  • the power delivered will often be in the range from 10 to 200W, usually being about 75W.
  • the temperature will usually not drop instantaneously when the heating energy stops, so that the tissue may remain at or near the therapy temperature for a time from about 10 seconds to about 2 minutes, and will often cool gradually back to body temperature .
  • Fig. 1 schematically illustrates a system 10 for shrinking a fascia F disposed between first and second adjacent tissues Tl, T2.
  • System 10 includes a pair of electrodes 12, 14 having large, substantially planar tissue engaging surfaces. Electrodes 12, 14 are aligned substantially parallel to each other with the fascia (and - adjacent tissues) disposed therebetween. The surfaces of electrodes 12, 14 which engage the tissue are cooled by a cooling system 16.
  • the cooling system will typically include a conduit through the electrode for the circulation of a cooling fluid, but may optionally rely on thermoelectric cooling or the like. The temperature of the electrode surface may be regulated by varying the temperature or flow rate of the cooling fluid.
  • Cooling may be provided through the use of an ice bath, by endothermic chemical reactions, by standard surgical room refrigeration mechanisms, or the like. Ideally, the cooling system cools an area which extends beyond the energized electrode surfaces to prevent any hot spots adjacent the tissue surface, and to maximize the heat removal from the tissue without chilling it to or below temperatures that irreversibly damage the tissue, such as might occur when freezing the tissue.
  • Each of the electrodes is separated into a plurality of electrode segments.
  • the electrode includes electrode segments 12a, 12b, 12c, 12d, and 12e, each of which is electrically isolated from the others. This allows the electrode segments to be individually energized. Electrodes 12, 14 are energized by a radiofrequency (RF) power source 18.
  • RF radiofrequency
  • Multiplexers 20 individually energize each electrode segment, typically varying the power or time each segment is energized to more nearly uniformly heat fascia F.
  • a controller 22 will typically include a computer program which directs the application of cooling flow and RF power through electrodes 12, 14, ideally based at least in part on a temperature signal sensed by a temperature sensor 24. Temperature sensor 24 may sense the temperature of the electrode, the tissue at the tissue/electrode interface, the intermediate tissue, or may alternatively sense the temperature of the fascia itself. Alternatively, the controller may direct the cooling/heating therapy in an open loop manner using dosimetry. The use of large cooled plate electrodes to direct an even electrical current flux can be understood with reference to the simplified cross-sectional illustration of Fig. 2.
  • the ideal geometry to provide a true one-dimensional temperature distribution would include large parallel plate electrodes having relatively minimal spacing therebetween.
  • the present invention can also make use of electrode geometries which vary somewhat from this ideal, particularly through the use of array electrodes.
  • the use of a single array electrode, in combination with a much larger, uncooled electrode pad may heat tissues disposed near the array, as will be described hereinbelow. Nonetheless, uniform heating is generally enhanced by providing electrode structures having tissue engaging surfaces which are as flat and/or as parallel as practical.
  • the parallel electrode surfaces will be separated by between about 1/3 and 5.0 times the width of the electrode surfaces (or of the smaller surface, if they are different) .
  • Fig. 2A schematically illustrates the shape of a target zone which is heated by selectively energizing only electrode segments 12c and 14c of cooled electrodes 12 and 14.
  • the temperature of target zone 32 (here illustrated schematically with isotemperature contour lines 30) is the result of uniform - heating between the energized electrode segments, in combination with cooling of tissue T by the electrode surfaces.
  • electrode segments 12a, 12b, 12c..., and 14a, 14b, 14c... can be energized, thereby heating an entire target zone 32 extending throughout tissue T between the electrodes.
  • the use of array electrodes provides still further flexibility regarding the selective targeting of tissues between electrodes 12 and 14.
  • selectively energizing a relatively large effective electrode surface by driving electrodes segments 12a, 12b, 12c, 12d, and 12e results in a low current flux which is widely disbursed throughout the tissue T engaged by electrode 12.
  • By driving this same current through a relatively small effective electrode surface using only a single electrode surface segment 14c produces an offset target zone 34 which is laterally smaller than and much closer to electrode 14 than to electrode 12.
  • Electrode 12 here comprises three electrode surface segments 12a, 12b, and 12c separated by insulating spaces 21.
  • a plastic housing 23 defines a flow path between a cooling inflow port 25 and a cooling outflow port 27, while heat - transfer between the cooling fluid and the electrode surface is enhanced by a thermally conductive front plate 29.
  • Front plate 29 generally comprises a thermally conductive metal such as aluminum.
  • Electrode surface segments 12a, 12b, and 12c may comprise surfaces of separated segments 31 of aluminum foil. Segments 31 may be electrically isolated and thermally coupled by a thin mylar insulation sheet 33 disposed between the segments and front plate 29.
  • the array electrode structures of the present invention will generally include a series of conductive surface segments which are aligned to define a substantially flat electrode surface.
  • the electrode surface segments are separated by an electrically insulating material, with the insulation being much smaller in surface area than the conductive segments.
  • the peripheral edges of the electrode segments may be rounded and/or covered by an insulating material to prevent concentrations of the electrical potential and injury to the engaged tissue surfaces.
  • the present invention also encompasses electrodes which are segmented into two-dimensional arrays. Where opposed sides of the tissue are accessible for relatively large array structures, such as along the exposed skin, or near the major cavities and orifices of the body, the electrode surfaces will preferably be separated by a gap which is less than a width (and length) of the electrodes.
  • one electrode structure may be disposed within a large body cavity such as the rectum or vagina, while the other is placed in an adjacent cavity, or on the skin so that the region to be treated is between the electrode surfaces.
  • one or both electrodes may be inserted and positioned laparoscopically-. It will often be desirable to clamp the tissue tightly between the electrodes to minimize the gap therebetween, and to promote efficient coupling of the electrode to the tissue.
  • the temperature profile of tissue T along an axis X between electrodes 12 and 14 is substantially uniform at body temperature (approximately 37nC) .
  • the tissue will preferably be pre-cooled by the surfaces of electrodes 12, 14, generally using an electrode surface temperature of at or above OnC .
  • Pre-cooling will substantially decrease the temperature of intermediate tissues 36, and will preferably at least partially decrease the temperature of stunned tissue 38. At least a portion of the target zone remains at or near the initial body temperature, as illustrated in Fig. 3B. Pre- cooling time will often depend on electrode separation and- tissue heat diffusivity. As will be explained in more detail regarding Figs.
  • pre-cooling (and/or pre-heating) of selective portions of the tissue engaged by a cooled electrode can alter the electrical current densities within tissues so as to provide selective, localized heating.
  • intermediate tissue 36 exhibits a substantial temperature differential as compared to target tissue 32.
  • the electrical impedance of an immediate tissue 36 has been enhanced relative to target tissue 32. This does not necessarily mean that the impedance of the intermediate tissue is now greater than that of the target tissue (although this will often be the case) .
  • the temperature differential between the target and intermediate tissues can now be used to help enhance selective heating of the target tissue while minimizing collateral damage to the adjacent tissue.
  • the RF current is directed through the tissue between the electrodes to heat the tissue.
  • a temperature sensor can be placed at the center of target zone 32 to help determine when the pre-cooling has been applied for the proper time to initiate RF heating.
  • the current flux applies a fairly uniform heating throughout the tissue between the electrodes, and the electrode surfaces are often cooled throughout the heating process.
  • target zone 32 has the highest temperature upon initiation of the heating cycle, and as the target zone is farthest from the cooled electrodes, a relatively small amount of heat flows from the target zone into the cooled electrodes, and the target zone is heated to a significantly higher temperature than intermediate tissue 36.
  • Heat is applied until the target zone is at or above a treatment temperature, typically resulting in a temperature distribution such as that illustrated in Fig. 3C.
  • a treatment temperature typically resulting in a temperature distribution such as that illustrated in Fig. 3C.
  • the cooling system continues to circulate cold fluid through the electrode, and to remove heat from the tissue, after the heating radiofrequency energy is halted.
  • substantially the entire tissue is below the maximum safe tissue temperature (as in Fig. 3D)
  • cooling can be halted, and the tissue can be allowed to return to standard body temperature, as illustrated in Fig. 3E.
  • RF current may be driven between the two cooled plate electrodes using intermittent pulses of excitation.
  • intermittent or pulsed excitation encompasses cyclically increasing and decreasing delivered power, including cyclical variations in RMS power provided by amplitude modulation, waveform shape modulation, pulse width modulation, or the like. Such intermittent excitation will preferably provide no more than about 25% of the RMS power of the pulses during the intervals between pulses.
  • the electrodes will be energized for between about 10 and 50% of a total heating session.
  • electrodes 12 and 14 may be energized for 15 sees, and then turned off for 15 sees, and then cycled on and off again repeatedly until the target tissue has been heated sufficiently to effect the desired shrinkage.
  • the electrode surfaces (and the surrounding probe structure which engages the tissue) will be cooled throughout the on/off cycles of the heating sessions.
  • the therapeutic heating and cooling provided by the electrodes of the present invention will often be verified and/or controlled by sensing the temperature of the target tissue and the adjacent tissue directly.
  • temperature sensing may be provided using a needle containing two temperature sensors: one at the tip to be positioned at the center of the treatment zone, and the second along the shaft of the needle so as to be positioned at the edge of the desired protection zone.
  • the second sensor will be placed along the border between the intermediate tissue and the target tissue, typically somewhere along stunned tissue 38.
  • the temperature sensors will preferably sense the tissue temperature during the intervals between pulses to minimize errors induced by the heating RF current flux in the surrounding tissue.
  • the temperature sensors may comprise thermistors, thermocouples, or the like.
  • the temperature sensing needle may be affixed to or advanceable from a probe supporting the electrode adjacent to or between the electrode segments. Alternatively, two or more needles may be used.
  • controller 22 will provide signals to cooling system 16 and the electrodes so that the electrodes chill the engaged tissue continually while the RF current is pulsed to increase the temperature of the treatment zone incrementally, ideally in a step-wise manner, until it reaches a temperature of 60nC or more, while at the same time limiting heating of the intermediate tissue to 45nC or less per the feedback from the needles.
  • pre-chilling time, the duration of the heat, the lengths of the heating intervals (and the time between heating intervals) during intermittent heating, and the radiofrequency heating current may be controlled without having direct feedback by using dosimetry. Where the thermal properties of these tissues are sufficiently predictable, the effect of treatment can be estimated from previous measurements.
  • endopelvic fascia EF defines a hammock- like structure which extends between the arcus tendineus fascia pelvis ATFP . These latter structures extend between the anterior and posterior portions of the pelvic bone, so that the endopelvic fascia EF largely defines the pelvic floor.
  • the bladder In women with urinary stress incontinence due to bladder neck hypermobility, the bladder has typically dropped between about 1.0 cm and 1.5 cm (or more) below its nominal position. This condition is typically due to weakening of the pelvic support structures, including the endopelvic fascia, the arcus tendineus fascia pelvis, and the surrounding ligaments and muscles, often as the result of bearing children.
  • the abdominal pressure When a woman with urinary stress incontinence sneezes, coughs, laughs, or exercises, the abdominal pressure often increases momentarily. Such pressure pulses force the bladder to descend still further, shortening the urethra UR and momentarily opening the urinary sphincter.
  • the present invention generally provides a therapy which applies gentle heating to shrink the length of the support tissues and return bladder B to its nominal position.
  • the bladder is still supported by the fascia, muscles, ligaments, and tendons of the body.
  • the endopelvic fascia EF and arcus tendineus fascia pelvis ATFP are controllably contracted to shrink them and re-elevate the bladder toward its original position.
  • bladder B can be seen to have dropped from its nominal position (shown in phantom by outline 36) . While endopelvic fascia EF still supports bladder B to maintain continence when the patient is at rest, a momentary pressure pulse P opens the bladder neck N, resulting in a release through urethra UR.
  • a known treatment for urinary stress incontinence relies on sutures S to hold bladder neck N closed so as to prevent inadvertent voiding, as seen in Fig. 4B.
  • Sutures S may be attached to bone anchors affixed to the pubic bone, ligaments higher in the pelvic region, or the like. In any case, loose sutures provide insufficient support of the bladder neck N and fail to overcome urinary stress incontinence, while overtightening of sutures S may make normal urination difficult and/or impossible.
  • Urethral probe 44 and vaginal probe 42 may optionally be coupleable to each other to facilitate aligning the probes on either side of the target tissue, either mechanically or by some remote sensing system.
  • one of the probes may include an ultrasound transducer, thereby facilitating alignment of the electrode surfaces and identification of the target tissue.
  • the proximal ends of the probes may attach together to align the electrodes and/or clamp the target tissue between the probes.
  • a mesh electrode 58 may be unfurled within the bladder in place of urethral probe 44.
  • Mesh electrode 58 preferably comprises a highly flexible conductive element, optionally being formed of a • shape memory alloy such as Nitinol".
  • the bladder may be filled with an electrically non-conductive fluid such as distilled water during the therapy, so that little or no RF current would flow into the bladder wall beyond the contact region between the electrode and the bladder.
  • an upper portion 58 of the mesh structure may be masked off electrically from the energized mesh surface of the lower portion.
  • Figs. 8A and 8B illustrate an optional deployable electrode support structure for use with vaginal probe 42.
  • Preheat electrodes EA and ED provide an initial preheat zone PH, as schematically shown in Fig.D$$.
  • Current is then alternated between interleaved electrode pairs EA, EC and EB, ED (as shown) to selectively heat overlapping target zones 32A, 32B.
  • the desired predetermined treatment temperature is achieved in a target tissue region 32C which is separated form the electrode surfaces.
  • a computer processor will generally control this heating process, as generally described above.
  • Figs. 12F and G illustrate a still further alternative bi-polar probe structure 84C which will produce a heating pattern that is appropriate for tumors and other relatively thick localized target tissues 32O .
  • target tissues 32O are separated from a tissue surface by an adjacent tissue AT.
  • Probe 84C includes concentric bi-polar electrodes 86C, shown here with one of the electrodes having a circular shape and the other having an annular shape .
  • the adjacent tissue will often be pre-cooled through the electrodes and/or the probe surface adjacent (and often between) the electrodes.
  • Figs. 12H-L illustrate a cooled bi-polar transvaginal probe with temperature sensing capabilities, and a method for its use to selectively heat and contract in a pelvic fascia.
  • Probe 84D include two needle mounted temperature sensors 95 extending from between electrodes 86D. The needle mounted temperature sensors are protected by a retractable guard 97 which is withdrawn proximately after probe 84D is inserted to the treatment location. The temperature sensors are then advanced into the tissue by moving the probe laterally as shown in Fig. 12K.
  • Probe 84D includes a cooling channel system 89 that cools the electrodes and the probe surface there between.
  • the bladder wall B will preferably be cooled by circulating a chilled fluid within the bladder (as described above in Fig. 6) , and pre-cooling of vaginal wall VW will often be computer controlled using feedback from the temperature sensors.
  • computer control based on this feedback might also (or instead) be provided to control pre-heating where preheating capabilities are included in the probe.
  • Temperature sensors 95 might be used to measures the temperature at the probe/interface, within the vaginal wall, within the endopelvic fascia, or the like. Regardless, pre-chilling of probe 84D and within bladder B will often be timed and controlled so as to provide a temperature profile similar to that illustrated in Fig. 3B upon the initiation of the heating current between electrodes 86D.
  • microwave probe 94 includes microwave antennas 96 which direct microwave heating energy 98 through the vaginal wall VW and onto endopelvic fascia EF.
  • Microwave probe 94 will again typically include a cooled probe surface to minimize damage to vaginal wall VW.
  • the microwave may optionally be produced by a phased array microwave antenna to decrease heating next to the cold probe relative to the heating of endopelvic fascia EF, or a more conventional microwave antenna may be used.
  • Microwave power having a frequency of about 2250 MHz is most often used for heating. However, the use of extremely high frequency microwaves would permit constructive interference at the intersection of microwave energy streams by control of the microwave frequency, phase, and electrode spacing.
  • Such constructive interference of microwaves may be used to enhance the heating of the target tissue relative to the heat produced in the intermediate tissue between microwave probe 94 and endopelvic fascia EF (in this example) .
  • Injection of an electrically insulating fluid, such as Dextran may be used to absorb microwave energy and protect tissues beyond the target zone.
  • injection of a liquid contrast medium might be used to enhance visualization of the treatment region, increasing the visibility and clarity of the vagina V, bladder B, the other adjacent organs, and the spaces therebetween.
  • a contrast medium will typically be highly visible under ultrasonic or fluoroscopic imaging modalities.
  • An alternative form of energy which may be used in a probe schematically similar to that illustrated in Fig. 13 is ultrasonic heating.
  • a cooled ultrasonic probe could be used to provide heating of the endopelvic fascia adjacent the vagina, preferably while protecting the adjacent tissues using a material which reflects ultrasound. Suitable protection materials include CO2 or a liquid/foam emulsion material.
  • High intensity ultrasound is able to heat tissues at a distance from the probe, and may be focused to apply the most intense heating at a particular treatment site. Concentration of ultrasound energy deep in the body may avoid heating of tissues at the entry site of the focused ultrasound beam, although gas pockets and bony structures may absorb and/or reflect the focused ultrasound energy, so that tissues may be damaged by both localized heating and cavitation.
  • the surface of an ultrasound probe will typically be cooled to protect the tissues which are directly engaged by the probe.
  • a focused ultrasound probe 300 having an elongate probe housing 302 is well adapted to accommodate axial translation 304 and rotation 306 of an ultrasound transducer 308.
  • the transducer can optionally be in the form of an annular array.
  • a fixed focal length transducer Such a fixed transducer will preferably be adapted to focus at a depth appropriate for the desired therapy. In some embodiments, it may be possible to translate such a fixed focal length transducer relative to the fascial layer to treat tissues at differing depths.
  • the transducer can be dynamically focused on the treatment region by phasing the excitation drive current to the array elements.
  • treatment may be performed using a continuous wave excitation, significantly facilitating phasing of the- drive currents to the individual array elements.
  • annular arrays are particularly well adapted for focusing ultrasound energy at a focus point 310. By varying the electrical current supplied to the individual annular shaped elements 312a, 312b,... of annular array 308 using phase control 314, the focal depth of the annular array can be increased to 310' or decreased to 310' ' .
  • ultrasound emitting structure is herein generally referred to as a transducer
  • ultrasound transmitters which do not also sense ultrasound energy might be used. Nonetheless, it may be advantageous to both image and heat the tissue using a single transducer structure.
  • the transducer may be excited with an impulse, or with a continuous signal where a longer duty cycle is desired. By alternating imaging and heating, the changes in the thickness or ultrasonic appearance of the tissue may be monitored to determine when the tissue has completed its treatment.
  • the ability to measure the thickness of fascia and other collagenated tissues using ultrasound energy is particularly advantageous for judging the completeness and/or efficacy of the thermal shrinking treatment.
  • heating may be controlled and terminated based on ultrasound feedback regarding the thickness and/or change in thickness of fascia or other collagenated tissues.
  • the generation of harmonics or subharmonics of the fundamental carrier frequency is an indication of the production of cavitation in the tissue, and may be used as a feedback mechanism for adjusting ultrasound power or scanning speed.
  • Ultrasound sensed target tissue thickness feedback and control may be incorporated into probes which heat the target tissue using ultrasound, RF energy, microwave, or any other energy transmitting mechanism, within the scope of the present invention.
  • an initial target tissue thickness may be measured and stored.
  • the thickness of the fascial layer (or other target tissue) can be remeasured, and the revised tissue depth may be compared to the initial tissue depth. Changes in a fascial layer tissue depth during treatment may then be used as a guide to the progress and completion of the tissue shrinkage operation. Depth determination may be made using an external imager, or might be provided by an imaging A-scan from the treatment transducer.
  • computer feedback may be used to guide the user in the application of ultrasound energy using ultrasound probe 300.
  • a computer controller may display the location of fixed reference points (such as bony structures) together with a representation of the physical location of the probe.
  • Such a display would help illustrate the location relative to the bony structures, which may help the user dynamically guide the probe to the desired treatment area.
  • a relative location image may be provided using an external ultrasonic imager.
  • the bony structures, the treatment probe, any temperature sensing needles, and the fascia or other target tissues could all be visible within a single image. This would greatly facilitate guiding of the probe, and may be used to selectively activate the probe so as to treat the target tissues, either manually by the user or automatically under computer control .
  • ultrasound transducer 300 is illustrated in more detail in Figs. 13D-G.
  • coolant flow 316 will preferably be provided through a cooling lumen 318, with the cooling lumen distributing a cooling fluid adjacent annular transducer 308.
  • cooling flow 316 which can protect intermediate tissues outside the treatment zone
  • it is highly beneficial to cool the transducer itself as transducers typically have an efficiency of about 60% or less.
  • the input power would typically be about 167W.
  • 67W of heat should be removed from the housing adjacent the transducer so as to prevent the surface of the transducer housing from rising above about 45nC.
  • the housing of the probe is defined by a thick lower wall 320 and a thin upper wall 322.
  • the use of a thinner upper wall, which will generally be disposed between transducer 308 and the target tissue, will enhance the efficiency of acoustic coupling between the transducer and the target tissue.
  • ultrasonic probes having a fixed, radially symmetrical transducer can be focused to a point having a size on the order of 1 wavelength.
  • Ultrasonic probes having transducers with cylindrically symmetrical designs will generally focus to a line with a theoretical thickness on the order of 1 wavelength, and with a length similar to the length of the cylindrical transducer.
  • a controller will coordinate the transducer drive current with the location, angle, and focusing depth of the transducer, so that the transducer is driven only while positioned such that the focus of the ultrasonic beam is within the target tissue.
  • the controller and the associated positioning mechanism will generally keep the array oriented toward and focused on the target tissue throughout much or all of the scan so that the transducer can be providing heat energy most of the time.
  • cooled bipolar electrodes 102 may optionally be formed as wide elongate plates. Grasping may be accomplished mechanically or by applying a vacuum to draw the vaginal wall into a cavity 104 of grasping probe 100. By drawing the endopelvic fascia into close proximity of both electrodes, a finer focusing of the heating may be accomplished, thereby minimizing the damage to adjacent tissues. Additionally, grasping probe 100 may draw the tissue inward to relieve any tension in the fascia, thereby enhancing the shrinkage. As described above regarding Fig. 12, C0 2 or some other insulating medium may be used for additional protection of adjacent tissues and organs.
  • a kit 110 includes vaginal probe 42 and instructions 112 for use of the probe to shrink tissues, the probe and instructions disposed in packaging 114.
  • the instructions may set forth the method steps for using probe 42 described hereinabove for selectively shrinking pelvic support tissues as a therapy for urinary incontinence, or may alternatively recite any of the other described methods. Additional elements for system 10 (see Fig. 1) may also be included in kit 110, or may be packaged separately. Instructions 112 will often comprise printed material, and may be found in whole or in part on packaging 114. Alternatively, instructions 112 may be in the form of a recording disk or other computer- readable data, a video tape, a sound recording, or the like. Referring now to Figs. 16A-C, a transurethral probe
  • Transurethral probe 150 may be used to shrink endopelvic fascia between bladder B and vagina V using a conductive fluid electrotherapy system 152.
  • Transurethral probe 150 includes a shaft 154 having an electrode 156 near its distal end.
  • a toroidal balloon 158 seals around the shaft to prevent fluid communication between bladder B and urethra UR.
  • Fluid in-flow and out -flow ports 160, 162 allow both gas and liquid to be introduced into the bladder in controlled amounts, and also allow a conductive fluid 164 (typically an electrolytic liquid, and ideally comprising a chilled saline solution) , to be circulated within the bladder.
  • a conductive fluid 164 typically an electrolytic liquid, and ideally comprising a chilled saline solution
  • An insulating fluid 166 having a density much less than that of conductive fluid 164 occupies a portion of bladder B away from the tissues targeted for treatment.
  • the conductive fluid can transmit RF current between the electrode and a cooled plate electrode of a vaginal probe 168.
  • the conductive properties of conductive fluid 164 may be optimized for both conduction of electricity (for example, by controlling the salinity of a saline solution) , and for directly transferring heat from the bladder wall .
  • transurethral probe 150 will be introduced through urethra UR to bladder B.
  • Toroidal balloon 158 can then be inflated to seal around the transurethral probe, and the bladder can be partially filled with insulating fluid 166, typically using air or a gas such as carbon dioxide.
  • the bladder is also partially filled with conductive fluid 164, typically in the form of a chilled electrolytic liquid such as saline.
  • the bladder wall may be further cooled by cycling the chilled saline before, during, and/or after heating, as generally - described above regarding Figs . 2 and 3.
  • the volumes of the fluids introduced into the bladder will be selected to provide therapy over the target tissue, and to minimize heating beyond the target tissue.
  • the volumes and positions of conductive fluid 164 and insulating fluid 166 are maintained throughout the procedure.
  • the conductive fluid effectively forms a large area electrode at the floor of the bladder, while the gas provides an electrical (and thermal) insulator at the top of the bladder. Maintaining the relative volumes of fluid limits heating to below a gas/liquid interface 184.
  • Transvaginal probe 168 is introduced and positioned to the extreme right or left side of the pelvis so that electrode 174 is oriented towards the interface between conductive fluid 164 and the lower right side or lower left side of the bladder wall. Probe balloon 172 can then be inflated, and the bladder wall and vaginal mucosa can be pre- chilled by circulating fluid through the probes. Once these tissues are properly pre-cooled, heating can proceed as described above, with the conductive fluid/bladder wall interface acting as one plate electrode, and electrode 174 on balloon 172 of vaginal probe 168 acting as the other. As was also described above, the electrode of vaginal probe 168 may be segmented to target heating on the target tissue, and to minimize any unwanted concentrations of heating caused by the variations in total tissue depth, non-parallel tissue surface effects, and the like.
  • a similar method for shrinking endopelvic fascia to that described above regarding Figs. 16A-C may be practiced using a transurethral probe having an inflatable spoon shaped balloon 200.
  • Spoon shaped balloon 200 supports a deployable electrode 202, and can be used to orient the deployable electrode toward vaginal probe 168. This may enhance control over the heating current flux, and spoon shaped balloon 200 (as well as balloon 172 of vaginal probe 168) may be insulated away from the electrode surface to further limit injury to the bladder wall.
  • Deployable electrode 202 may also be segmented as described above, and will provide a small cross-sectional profile prior to inflation so as to minimize trauma during insertion.
  • a two probe device 250 is illustrated in Fig. 18A.
  • Two probe device 250 will be used in a method similar to that described above with reference to Fig. 6, but here includes both a transvaginal probe 252 and a transrectal probe 254.
  • Each of these probes includes a proximal end 256 and a distal end 258.
  • the distal ends are sized and shaped for insertion into their respective body cavities.
  • Proximal ends 256 are mechanically coupled by a clamp structure 260.
  • Rotating a handle 262 of clamp structure 260 changes a separation distance 264 between electrodes 266, 268 via threads 270.
  • clamping structure 260 helps maintain the parallel alignment between the electrodes, and also helps to compress the tissue between the electrode surfaces. It should be understood that a wide variety of mechanical actuators might be used in place of the threaded mechanism illustrated in Fig. 18A.
  • Parallel bar linkages, ratcheted sliding joints, rack-and-pinion mechanisms, and recirculating ball linear actuators are just a few examples of alternative mechanisms which might be used.
  • the probes may be inserted independently, and then coupled together using a releasable clamping structure.
  • a needle mounted temperature sensor 278 may be advanced into the clamped tissue from adjacent one electrode to provide feedback on the heating/cooling of tissues. Such temperature information may be transmitted to a controller using temperature sensor wires 280. RF energy will be transmitted down the probes via electrode conductors 282.
  • two probe clamp 250 will be positioned with one of the probes extending into the rectum, and the other probe extending into the vagina.
  • Clamping structure 260 will be actuated using handle 262 to decrease the separation distance 264, and to clamp the target tissue between electrodes 266, 268.
  • Needle mounted temperature sensor 278 will extend into the clamped tissue, ideally extending into the target tissue.
  • the clamp structure is sufficiently stiff to maintain the electrode structures substantially in alignment, and also to maintain the electrode surfaces roughly parallel to each other, so as to be capable of providing sufficiently uniform current flux to shrink the target tissue.
  • the clamping structure may accommodate significant angularity between the electrode surfaces, as well as some axial and lateral misalignment, while still effectively heating and shrinking the target tissue with minimal collateral damage.
  • electrodes 266, 268 are positioned at closer proximity to each other than probes 252, 254 proximal of the electrodes. This avoids injury to tissues proximal of the electrodes, particularly to the rectal and vaginal sphincters, when the clamping mechanism brings the probes together.
  • two probe device 250 is illustrated having two separate probes which are both adapted for insertion into the body, it should be understood that a similar clamping structure may make use of a single insertable probe carrying an electrode, and a second electrode support structure adapted for use on the exposed skin.
  • Fig. 18A is particularly suitable for use as a therapy for rectocele. Similar probe structures will find use in a wide variety of applications, including many of those described above, as well as those described in U.S. Patent Application No. 08/910,370, filed August 13, 1997, previously incorporated by reference.
  • the vaginal wall (including the endopelvic fascia) may be drawn downward between a pair of electrodes for selectively shrinking of the pelvic support tissues as a therapy for incontinence. Similar therapies may be possible for the colon.
  • an 0 ring may be sized to fittingly engage the surrounding vaginal wall so as to provide mechanical stabilization.
  • Such an O ring may be variable in size, or may be available in a variety of selectable sizes.
  • mechanical stabilization may be provided using an inflatable cuff disposed around the shaft of the probe. Such a cuff could be inflated after the probe is positioned to engage the surrounding tissue to provide mechanical stabilization.
  • An adhesive surface or sticky pad on the probe may allow the probe to adhere to the inner vaginal surface. It may be preferable to adhesively affix only a portion of the probe, particularly where an alternate portion can translate and/or rotate with respect to the fixed portion. This might permit the treatment region to be conveniently controlled with reference to the fixed portion. A similar (and more readily releasable) result may be provided by using a vacuum attachment mechanism.
  • Such needle electrodes will preferably include radially expandable structures such as balloons supporting the conductive distal regions. This allows a radius of curvature of the conductive distal regions to be increased by inflating the balloons once the needles are in position. By increasing the radius of curvature sufficiently relative to the separation between electrodes, the spatial uniformity of the heating can be enhanced. Chilled balloon inflation fluid can limit heating of the tissue adjacent the balloon.

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Abstract

Cette invention se rapporte à des dispositifs, procédés et systèmes perfectionnés permettant de resserrer des tissus renfermant du collagène et, en particulier de traiter l'incontinence urinaire de manière non effractive grâce à l'orientation de l'énergie en direction des tissus de soutien du patient. Cette énergie chauffe les fascia et d'autres tissus de soutien renfermant du collagène, ce qui les fait se contracter. Cette énergie peut être appliquée de manière intermittente, souvent entre une paire de grandes électrodes à plaque présentant des surfaces plates refroidies, ces électrodes étant éventuellement soutenues par une structure clamp. Ces électrodes à plaque refroidies sont capables d'orienter de l'énergie électrique dans des tissus intermédiaires et dans les fascia alors que la surface de l'électrode refroidie empêche de léser les tissus intermédiaires, en particulier lorsque les surfaces de l'électrode sont refroidies avant, pendant et après un cycle de chauffage intermittent. Idéalement, l'électrode à plaque comporte un réseau de segments de surfaces d'électrodes séparés de sorte que le flux de courant peut être modifié en vue de cibler de manière sélective les fascia. Selon un autre mode de réalisation, les 'électrodes liquides' réfrigérées peuvent orienter le courant dans une partie sélectionnée de la vessie tout en refroidissant également la paroi de la vessie. Un gaz isolant peut empêcher la chauffage d'une autre partie de la vessie et de ses tissus adjacents, et/ou des transducteurs ultrasonores orientent l'énergie dans des tissus intermédiaires et dans les fascia sans léser, ou peu, les tissus intermédiaires.
PCT/US1998/016754 1997-08-13 1998-08-12 Dispositifs, procedes et systemes non effractifs permettant de resserrer des tissus WO1999008614A1 (fr)

Priority Applications (5)

Application Number Priority Date Filing Date Title
CA002300152A CA2300152A1 (fr) 1997-08-13 1998-08-12 Dispositifs, procedes et systemes non effractifs permettant de resserrer des tissus
JP2000509360A JP2001514921A (ja) 1997-08-13 1998-08-12 組織収縮のための非侵襲性デバイス、方法、およびシステム
DE69834644T DE69834644T2 (de) 1997-08-13 1998-08-12 Nichtinvasive geräte und systeme zum schrumpfen von geweben
AU91038/98A AU732188B2 (en) 1997-08-13 1998-08-12 Noninvasive devices, methods, and systems for shrinking of tissues
EP98943191A EP1003432B1 (fr) 1997-08-13 1998-08-12 Dispositifs et systemes non effractifs permettant de resserrer des tissus

Applications Claiming Priority (14)

Application Number Priority Date Filing Date Title
US08/910,369 US6035238A (en) 1997-08-13 1997-08-13 Noninvasive devices, methods, and systems for shrinking of tissues
US08/910,369 1997-08-13
US08/910,775 1997-08-13
US08/910,371 US6081749A (en) 1997-08-13 1997-08-13 Noninvasive devices, methods, and systems for shrinking of tissues
US08/910,775 US6480746B1 (en) 1997-08-13 1997-08-13 Noninvasive devices, methods, and systems for shrinking of tissues
US08/910,371 1997-08-13
US7141998P 1998-01-14 1998-01-14
US7141898P 1998-01-14 1998-01-14
US7142298P 1998-01-14 1998-01-14
US7132398P 1998-01-14 1998-01-14
US60/071,422 1998-01-14
US60/071,419 1998-01-14
US60/071,323 1998-01-14
US60/071,418 1998-01-14

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CA (1) CA2300152A1 (fr)
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Cited By (29)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0983751A1 (fr) * 1998-08-30 2000-03-08 Moshe Ein-Gal Appareil de coagulation pour varices
WO2000023127A1 (fr) 1998-10-19 2000-04-27 Surx, Inc. Systeme de diagnostic de l'incontinence urinaire
WO2000053113A1 (fr) * 1999-03-09 2000-09-14 Thermage, Inc. Appareil et procede destines au traitement de tissus
WO2000078241A1 (fr) * 1999-06-23 2000-12-28 Novasys Medical, Inc. Traitement des sphincters par electrochirurgie et principes actifs
WO2001000269A1 (fr) * 1999-06-30 2001-01-04 Thermage, Inc. Distributeur de fluide
EP1281366A3 (fr) * 1999-06-23 2003-03-19 Novasys Medical, Inc. Traitement des sphinctères avec l'électrochirurgie et des substances actives
WO2003065916A1 (fr) * 2002-02-06 2003-08-14 Thermage, Inc. Instrument a main pour traiter un tissu par radiofrequence
WO2004032775A1 (fr) * 2002-08-26 2004-04-22 Yoshifumi Fujinaka Dispositif therapeutique ultrasonore puissant a action concentree
US7006874B2 (en) 1996-01-05 2006-02-28 Thermage, Inc. Treatment apparatus with electromagnetic energy delivery device and non-volatile memory
US7022121B2 (en) 1999-03-09 2006-04-04 Thermage, Inc. Handpiece for treatment of tissue
US7115123B2 (en) 1996-01-05 2006-10-03 Thermage, Inc. Handpiece with electrode and non-volatile memory
EP1722703A2 (fr) * 2004-03-10 2006-11-22 AMS Research Corporation Traitement d'incontinence par guide uretral
US7189230B2 (en) 1996-01-05 2007-03-13 Thermage, Inc. Method for treating skin and underlying tissue
US7229436B2 (en) 1996-01-05 2007-06-12 Thermage, Inc. Method and kit for treatment of tissue
US7267675B2 (en) 1996-01-05 2007-09-11 Thermage, Inc. RF device with thermo-electric cooler
US7452358B2 (en) 1996-01-05 2008-11-18 Thermage, Inc. RF electrode assembly for handpiece
US7473251B2 (en) 1996-01-05 2009-01-06 Thermage, Inc. Methods for creating tissue effect utilizing electromagnetic energy and a reverse thermal gradient
US8465482B2 (en) 2000-10-02 2013-06-18 Verathon, Inc. Apparatus and methods for treating female urinary incontinence
US8740846B2 (en) 1996-09-20 2014-06-03 Verathon, Inc. Treatment of tissue in sphincters, sinuses, and orifices
US8961511B2 (en) 2006-02-07 2015-02-24 Viveve, Inc. Vaginal remodeling device and methods
US9023031B2 (en) 1997-08-13 2015-05-05 Verathon Inc. Noninvasive devices, methods, and systems for modifying tissues
US9271785B2 (en) 2009-09-18 2016-03-01 Viveve, Inc. Vaginal remodeling device and methods
US9415235B2 (en) 2012-03-16 2016-08-16 Viveve, Inc. Vaginal remodeling device and method
US9468499B2 (en) 2003-07-18 2016-10-18 Covidien Lp Devices and methods for cooling microwave antennas
EP2568901A4 (fr) * 2010-05-14 2016-12-21 Rainbow Medical Ltd Traitement et surveillance par ultrasons facilités par la réflexion
US11511110B2 (en) 2018-06-27 2022-11-29 Viveve, Inc. Methods for treating urinary stress incontinence
US11529189B2 (en) 2014-05-23 2022-12-20 Hologic, Inc. Methods and devices for treating pelvic conditions
US11826517B2 (en) 2016-10-18 2023-11-28 Boston Scientific Scimed, Inc. Guide extension catheter
US11896823B2 (en) 2017-04-04 2024-02-13 Btl Healthcare Technologies A.S. Method and device for pelvic floor tissue treatment

Families Citing this family (566)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5345170A (en) 1992-06-11 1994-09-06 Cascade Microtech, Inc. Wafer probe station having integrated guarding, Kelvin connection and shielding systems
US6380751B2 (en) 1992-06-11 2002-04-30 Cascade Microtech, Inc. Wafer probe station having environment control enclosure
US6161543A (en) 1993-02-22 2000-12-19 Epicor, Inc. Methods of epicardial ablation for creating a lesion around the pulmonary veins
US5561377A (en) 1995-04-14 1996-10-01 Cascade Microtech, Inc. System for evaluating probing networks
US6232789B1 (en) 1997-05-28 2001-05-15 Cascade Microtech, Inc. Probe holder for low current measurements
US20030212393A1 (en) * 1996-01-05 2003-11-13 Knowlton Edward W. Handpiece with RF electrode and non-volatile memory
US6289249B1 (en) * 1996-04-17 2001-09-11 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Transcatheter microwave antenna
US5914613A (en) 1996-08-08 1999-06-22 Cascade Microtech, Inc. Membrane probing system with local contact scrub
US6840936B2 (en) * 1996-10-22 2005-01-11 Epicor Medical, Inc. Methods and devices for ablation
US6719755B2 (en) 1996-10-22 2004-04-13 Epicor Medical, Inc. Methods and devices for ablation
US6311692B1 (en) 1996-10-22 2001-11-06 Epicor, Inc. Apparatus and method for diagnosis and therapy of electrophysiological disease
US7052493B2 (en) 1996-10-22 2006-05-30 Epicor Medical, Inc. Methods and devices for ablation
US5904651A (en) 1996-10-28 1999-05-18 Ep Technologies, Inc. Systems and methods for visualizing tissue during diagnostic or therapeutic procedures
US6292700B1 (en) 1999-09-10 2001-09-18 Surx, Inc. Endopelvic fascia treatment for incontinence
US6033399A (en) * 1997-04-09 2000-03-07 Valleylab, Inc. Electrosurgical generator with adaptive power control
US6002263A (en) 1997-06-06 1999-12-14 Cascade Microtech, Inc. Probe station having inner and outer shielding
US6104959A (en) 1997-07-31 2000-08-15 Microwave Medical Corp. Method and apparatus for treating subcutaneous histological features
EP1003432B1 (fr) * 1997-08-13 2006-05-24 Solarant Medical, Inc. Dispositifs et systemes non effractifs permettant de resserrer des tissus
US20030178032A1 (en) * 1997-08-13 2003-09-25 Surx, Inc. Noninvasive devices, methods, and systems for shrinking of tissues
US6050943A (en) 1997-10-14 2000-04-18 Guided Therapy Systems, Inc. Imaging, therapy, and temperature monitoring ultrasonic system
US8709007B2 (en) 1997-10-15 2014-04-29 St. Jude Medical, Atrial Fibrillation Division, Inc. Devices and methods for ablating cardiac tissue
DE69941252D1 (de) * 1998-01-14 2009-09-24 Ams Res Corp Geriffelte elektroden
US6685640B1 (en) * 1998-03-30 2004-02-03 Focus Surgery, Inc. Ablation system
US6256882B1 (en) 1998-07-14 2001-07-10 Cascade Microtech, Inc. Membrane probing system
CA2243382A1 (fr) * 1998-07-16 2000-01-16 Universite De Montreal Procede et structure d'electrode pour reduire l'influence des parasites induit par le mouvement des electrodes
US8308719B2 (en) 1998-09-21 2012-11-13 St. Jude Medical, Atrial Fibrillation Division, Inc. Apparatus and method for ablating tissue
US7137980B2 (en) 1998-10-23 2006-11-21 Sherwood Services Ag Method and system for controlling output of RF medical generator
US7901400B2 (en) 1998-10-23 2011-03-08 Covidien Ag Method and system for controlling output of RF medical generator
US7364577B2 (en) 2002-02-11 2008-04-29 Sherwood Services Ag Vessel sealing system
US6578264B1 (en) 1999-06-04 2003-06-17 Cascade Microtech, Inc. Method for constructing a membrane probe using a depression
US6445202B1 (en) 1999-06-30 2002-09-03 Cascade Microtech, Inc. Probe station thermal chuck with shielding for capacitive current
EP1207788A4 (fr) 1999-07-19 2009-12-09 St Jude Medical Atrial Fibrill Techniques d'ablation de tissus et dispositif correspondant
US6587730B2 (en) * 1999-07-27 2003-07-01 Mattioli Engineering Ltd. Method and apparatus for skin brown spot removal and collagen formation
US8241274B2 (en) 2000-01-19 2012-08-14 Medtronic, Inc. Method for guiding a medical device
US6838890B2 (en) 2000-02-25 2005-01-04 Cascade Microtech, Inc. Membrane probing system
US8048070B2 (en) 2000-03-06 2011-11-01 Salient Surgical Technologies, Inc. Fluid-assisted medical devices, systems and methods
US7811282B2 (en) 2000-03-06 2010-10-12 Salient Surgical Technologies, Inc. Fluid-assisted electrosurgical devices, electrosurgical unit with pump and methods of use thereof
US6953461B2 (en) 2002-05-16 2005-10-11 Tissuelink Medical, Inc. Fluid-assisted medical devices, systems and methods
EP1946716B1 (fr) 2000-03-06 2017-07-19 Salient Surgical Technologies, Inc. Système d'alimentation de fluide et contrôleur pour dispositif électrochirurgicaux
US6689131B2 (en) * 2001-03-08 2004-02-10 Tissuelink Medical, Inc. Electrosurgical device having a tissue reduction sensor
US6558385B1 (en) 2000-09-22 2003-05-06 Tissuelink Medical, Inc. Fluid-assisted medical device
US6965226B2 (en) 2000-09-05 2005-11-15 Cascade Microtech, Inc. Chuck for holding a device under test
US6914423B2 (en) 2000-09-05 2005-07-05 Cascade Microtech, Inc. Probe station
DE20114544U1 (de) 2000-12-04 2002-02-21 Cascade Microtech, Inc., Beaverton, Oreg. Wafersonde
US6951569B2 (en) * 2000-12-27 2005-10-04 Ethicon, Inc. Surgical balloon having varying wall thickness
US7914453B2 (en) 2000-12-28 2011-03-29 Ardent Sound, Inc. Visual imaging system for ultrasonic probe
US6970634B2 (en) * 2001-05-04 2005-11-29 Cascade Microtech, Inc. Fiber optic wafer probe
US7846096B2 (en) 2001-05-29 2010-12-07 Ethicon Endo-Surgery, Inc. Method for monitoring of medical treatment using pulse-echo ultrasound
US20030092988A1 (en) * 2001-05-29 2003-05-15 Makin Inder Raj S. Staging medical treatment using ultrasound
WO2003052435A1 (fr) 2001-08-21 2003-06-26 Cascade Microtech, Inc. Systeme de detection a membrane
US6953469B2 (en) * 2001-08-30 2005-10-11 Ethicon, Inc, Device and method for treating intraluminal tissue
US6758831B2 (en) 2001-09-24 2004-07-06 Ethicon, Inc. Device and method for aligning with the tubal ostium
US6685623B2 (en) 2001-11-20 2004-02-03 Surx, Inc. Incontinence treatment with urethral guide
US20060205996A1 (en) * 2001-11-20 2006-09-14 Solorant Medical, Inc. Incontinence treatment with urethral guide
US7311708B2 (en) 2001-12-12 2007-12-25 Tissuelink Medical, Inc. Fluid-assisted medical devices, systems and methods
US6777964B2 (en) 2002-01-25 2004-08-17 Cascade Microtech, Inc. Probe station
US6799063B2 (en) * 2002-02-27 2004-09-28 Medivance Incorporated Temperature control pads with integral electrodes
US8882755B2 (en) 2002-03-05 2014-11-11 Kimberly-Clark Inc. Electrosurgical device for treatment of tissue
US7294127B2 (en) 2002-03-05 2007-11-13 Baylis Medical Company Inc. Electrosurgical tissue treatment method
US8043287B2 (en) 2002-03-05 2011-10-25 Kimberly-Clark Inc. Method of treating biological tissue
US6896675B2 (en) 2002-03-05 2005-05-24 Baylis Medical Company Inc. Intradiscal lesioning device
US8518036B2 (en) 2002-03-05 2013-08-27 Kimberly-Clark Inc. Electrosurgical tissue treatment method
US6882885B2 (en) 2002-03-19 2005-04-19 Solarant Medical, Inc. Heating method for tissue contraction
NL1021183C2 (nl) * 2002-03-20 2003-09-23 Martil Instr B V Katheter met geïntegreerd signaal verwerkingsapparaat.
IL148791A0 (en) * 2002-03-20 2002-09-12 Yoni Iger Method and apparatus for altering activity of tissue layers
US8150519B2 (en) 2002-04-08 2012-04-03 Ardian, Inc. Methods and apparatus for bilateral renal neuromodulation
US7617005B2 (en) 2002-04-08 2009-11-10 Ardian, Inc. Methods and apparatus for thermally-induced renal neuromodulation
US8347891B2 (en) 2002-04-08 2013-01-08 Medtronic Ardian Luxembourg S.A.R.L. Methods and apparatus for performing a non-continuous circumferential treatment of a body lumen
US7756583B2 (en) 2002-04-08 2010-07-13 Ardian, Inc. Methods and apparatus for intravascularly-induced neuromodulation
US7056318B2 (en) * 2002-04-12 2006-06-06 Reliant Technologies, Inc. Temperature controlled heating device and method to heat a selected area of a biological body
JP2005527823A (ja) 2002-05-23 2005-09-15 カスケード マイクロテック インコーポレイテッド デバイスのテスト用プローブ
US20040082859A1 (en) 2002-07-01 2004-04-29 Alan Schaer Method and apparatus employing ultrasound energy to treat body sphincters
US6852110B2 (en) * 2002-08-01 2005-02-08 Solarant Medical, Inc. Needle deployment for temperature sensing from an electrode
US8361067B2 (en) * 2002-09-30 2013-01-29 Relievant Medsystems, Inc. Methods of therapeutically heating a vertebral body to treat back pain
US7258690B2 (en) 2003-03-28 2007-08-21 Relievant Medsystems, Inc. Windowed thermal ablation probe
US6907884B2 (en) 2002-09-30 2005-06-21 Depay Acromed, Inc. Method of straddling an intraosseous nerve
US20040133195A1 (en) * 2002-10-03 2004-07-08 Stephen Solomon Percutaneous surgical instruments and methods using the same
US7931649B2 (en) 2002-10-04 2011-04-26 Tyco Healthcare Group Lp Vessel sealing instrument with electrical cutting mechanism
EP1572020A4 (fr) 2002-10-29 2006-05-03 Tissuelink Medical Inc Ciseaux electrochirurgicaux utilisant un fluide et leurs procedes d'utilisation
US6847219B1 (en) 2002-11-08 2005-01-25 Cascade Microtech, Inc. Probe station with low noise characteristics
US6724205B1 (en) 2002-11-13 2004-04-20 Cascade Microtech, Inc. Probe for combined signals
US7799026B2 (en) 2002-11-14 2010-09-21 Covidien Ag Compressible jaw configuration with bipolar RF output electrodes for soft tissue fusion
US7250779B2 (en) 2002-11-25 2007-07-31 Cascade Microtech, Inc. Probe station with low inductance path
US7044948B2 (en) 2002-12-10 2006-05-16 Sherwood Services Ag Circuit for controlling arc energy from an electrosurgical generator
US6861856B2 (en) 2002-12-13 2005-03-01 Cascade Microtech, Inc. Guarded tub enclosure
US7131445B2 (en) 2002-12-23 2006-11-07 Gyrus Medical Limited Electrosurgical method and apparatus
US7315762B2 (en) * 2003-01-16 2008-01-01 American Medical Systems, Inc. Non-surgical incontinence treatment system and method
JP2004230033A (ja) * 2003-01-31 2004-08-19 Toshiba Corp 超音波探触子再分極装置、超音波プローブ及び超音波診断装置
AU2004235739B2 (en) 2003-05-01 2010-06-17 Covidien Ag Method and system for programming and controlling an electrosurgical generator system
AU2004237772B2 (en) 2003-05-01 2009-12-10 Covidien Ag Electrosurgical instrument which reduces thermal damage to adjacent tissue
US7221172B2 (en) 2003-05-06 2007-05-22 Cascade Microtech, Inc. Switched suspended conductor and connection
US20040226556A1 (en) 2003-05-13 2004-11-18 Deem Mark E. Apparatus for treating asthma using neurotoxin
WO2004103230A1 (fr) * 2003-05-22 2004-12-02 Medoc Ltd. Sonde et procede de stimulation thermique
US7057404B2 (en) 2003-05-23 2006-06-06 Sharp Laboratories Of America, Inc. Shielded probe for testing a device under test
US7492172B2 (en) 2003-05-23 2009-02-17 Cascade Microtech, Inc. Chuck for holding a device under test
US7569626B2 (en) 2003-06-05 2009-08-04 Dfine, Inc. Polymer composites for biomedical applications and methods of making
US7662099B2 (en) * 2003-06-30 2010-02-16 Ethicon, Inc. Method and instrumentation to sense thermal lesion formation by ultrasound imaging
US7722600B2 (en) * 2003-08-25 2010-05-25 Cutera, Inc. System and method for heating skin using light to provide tissue treatment
US8870856B2 (en) * 2003-08-25 2014-10-28 Cutera, Inc. Method for heating skin using light to provide tissue treatment
US8915906B2 (en) * 2003-08-25 2014-12-23 Cutera, Inc. Method for treatment of post-partum abdominal skin redundancy or laxity
DE202004021947U1 (de) * 2003-09-12 2013-05-13 Vessix Vascular, Inc. Auswählbare exzentrische Remodellierung und/oder Ablation von atherosklerotischem Material
US7250626B2 (en) 2003-10-22 2007-07-31 Cascade Microtech, Inc. Probe testing structure
US8104956B2 (en) 2003-10-23 2012-01-31 Covidien Ag Thermocouple measurement circuit
US7396336B2 (en) 2003-10-30 2008-07-08 Sherwood Services Ag Switched resonant ultrasonic power amplifier system
US9848938B2 (en) 2003-11-13 2017-12-26 Covidien Ag Compressible jaw configuration with bipolar RF output electrodes for soft tissue fusion
US7367976B2 (en) 2003-11-17 2008-05-06 Sherwood Services Ag Bipolar forceps having monopolar extension
US7131970B2 (en) 2003-11-19 2006-11-07 Sherwood Services Ag Open vessel sealing instrument with cutting mechanism
US7131860B2 (en) 2003-11-20 2006-11-07 Sherwood Services Ag Connector systems for electrosurgical generator
US8206304B1 (en) * 2003-12-16 2012-06-26 Vascular Technology Incorporated Doppler transceiver and probe for use in minimally invasive procedures
US7187188B2 (en) 2003-12-24 2007-03-06 Cascade Microtech, Inc. Chuck with integrated wafer support
DE202004021093U1 (de) 2003-12-24 2006-09-28 Cascade Microtech, Inc., Beaverton Aktiver Halbleiterscheibenmessfühler
US7251531B2 (en) * 2004-01-30 2007-07-31 Ams Research Corporation Heating method for tissue contraction
US7476242B2 (en) * 2004-01-30 2009-01-13 Ams Research Corporation Electrically heated/phase change probe temperature control
US7727232B1 (en) 2004-02-04 2010-06-01 Salient Surgical Technologies, Inc. Fluid-assisted medical devices and methods
US8165695B2 (en) * 2004-02-11 2012-04-24 Ethicon, Inc. System and method for selectively stimulating different body parts
US8751003B2 (en) * 2004-02-11 2014-06-10 Ethicon, Inc. Conductive mesh for neurostimulation
US7979137B2 (en) 2004-02-11 2011-07-12 Ethicon, Inc. System and method for nerve stimulation
US7780662B2 (en) 2004-03-02 2010-08-24 Covidien Ag Vessel sealing system using capacitive RF dielectric heating
US7247141B2 (en) * 2004-03-08 2007-07-24 Ethicon Endo-Surgery, Inc. Intra-cavitary ultrasound medical system and method
US20050203416A1 (en) * 2004-03-10 2005-09-15 Angelsen Bjorn A. Extended, ultrasound real time 2D imaging probe for insertion into the body
US20090247879A1 (en) * 2004-03-09 2009-10-01 Angelsen Bjorn A J Extended ultrasound imaging probe for insertion into the body
EP2343021A1 (fr) 2004-04-01 2011-07-13 The General Hospital Corporation Procédé et appareil pour le traitement dermatologique et le remodelage des tissus
US20050228286A1 (en) * 2004-04-07 2005-10-13 Messerly Jeffrey D Medical system having a rotatable ultrasound source and a piercing tip
US20050240123A1 (en) * 2004-04-14 2005-10-27 Mast T D Ultrasound medical treatment system and method
US20050234305A1 (en) * 2004-04-15 2005-10-20 Frederick Licciardi Medical device and system for providing an image
US20050234438A1 (en) * 2004-04-15 2005-10-20 Mast T D Ultrasound medical treatment system and method
US20050240124A1 (en) * 2004-04-15 2005-10-27 Mast T D Ultrasound medical treatment system and method
US7494467B2 (en) * 2004-04-16 2009-02-24 Ethicon Endo-Surgery, Inc. Medical system having multiple ultrasound transducers or an ultrasound transducer and an RF electrode
US20050251116A1 (en) * 2004-05-05 2005-11-10 Minnow Medical, Llc Imaging and eccentric atherosclerotic material laser remodeling and/or ablation catheter
US8333764B2 (en) * 2004-05-12 2012-12-18 Medtronic, Inc. Device and method for determining tissue thickness and creating cardiac ablation lesions
US8235909B2 (en) 2004-05-12 2012-08-07 Guided Therapy Systems, L.L.C. Method and system for controlled scanning, imaging and/or therapy
US20050256405A1 (en) * 2004-05-17 2005-11-17 Makin Inder Raj S Ultrasound-based procedure for uterine medical treatment
US7883468B2 (en) * 2004-05-18 2011-02-08 Ethicon Endo-Surgery, Inc. Medical system having an ultrasound source and an acoustic coupling medium
US7951095B2 (en) * 2004-05-20 2011-05-31 Ethicon Endo-Surgery, Inc. Ultrasound medical system
US20050261587A1 (en) * 2004-05-20 2005-11-24 Makin Inder R S Ultrasound medical system and method
US7473250B2 (en) * 2004-05-21 2009-01-06 Ethicon Endo-Surgery, Inc. Ultrasound medical system and method
US7695436B2 (en) * 2004-05-21 2010-04-13 Ethicon Endo-Surgery, Inc. Transmit apodization of an ultrasound transducer array
US20050261588A1 (en) * 2004-05-21 2005-11-24 Makin Inder Raj S Ultrasound medical system
DE202005021434U1 (de) 2004-06-07 2008-03-20 Cascade Microtech, Inc., Beaverton Thermooptische Einspannvorrichtung
US7330041B2 (en) 2004-06-14 2008-02-12 Cascade Microtech, Inc. Localizing a temperature of a device for testing
US7806839B2 (en) 2004-06-14 2010-10-05 Ethicon Endo-Surgery, Inc. System and method for ultrasound therapy using grating lobes
US7368927B2 (en) 2004-07-07 2008-05-06 Cascade Microtech, Inc. Probe head having a membrane suspended probe
US20060047281A1 (en) 2004-09-01 2006-03-02 Syneron Medical Ltd. Method and system for invasive skin treatment
US7438261B2 (en) * 2004-09-09 2008-10-21 David R. Porter Stratospheric balloon utilizing electrostatic inflation of walls
US8396548B2 (en) 2008-11-14 2013-03-12 Vessix Vascular, Inc. Selective drug delivery in a lumen
US9713730B2 (en) 2004-09-10 2017-07-25 Boston Scientific Scimed, Inc. Apparatus and method for treatment of in-stent restenosis
WO2006031646A2 (fr) 2004-09-13 2006-03-23 Cascade Microtech, Inc. Structures pour sonder deux cotes d'un dispositif
US7824348B2 (en) 2004-09-16 2010-11-02 Guided Therapy Systems, L.L.C. System and method for variable depth ultrasound treatment
US7393325B2 (en) 2004-09-16 2008-07-01 Guided Therapy Systems, L.L.C. Method and system for ultrasound treatment with a multi-directional transducer
US9011336B2 (en) 2004-09-16 2015-04-21 Guided Therapy Systems, Llc Method and system for combined energy therapy profile
US7530958B2 (en) 2004-09-24 2009-05-12 Guided Therapy Systems, Inc. Method and system for combined ultrasound treatment
US10864385B2 (en) 2004-09-24 2020-12-15 Guided Therapy Systems, Llc Rejuvenating skin by heating tissue for cosmetic treatment of the face and body
US8535228B2 (en) 2004-10-06 2013-09-17 Guided Therapy Systems, Llc Method and system for noninvasive face lifts and deep tissue tightening
US8444562B2 (en) 2004-10-06 2013-05-21 Guided Therapy Systems, Llc System and method for treating muscle, tendon, ligament and cartilage tissue
US7530356B2 (en) * 2004-10-06 2009-05-12 Guided Therapy Systems, Inc. Method and system for noninvasive mastopexy
EP2279698A3 (fr) * 2004-10-06 2014-02-19 Guided Therapy Systems, L.L.C. Procédé et système pour l'amélioration cosmétique non invasive de vergetures
US11883688B2 (en) 2004-10-06 2024-01-30 Guided Therapy Systems, Llc Energy based fat reduction
US20060111744A1 (en) 2004-10-13 2006-05-25 Guided Therapy Systems, L.L.C. Method and system for treatment of sweat glands
US8690778B2 (en) 2004-10-06 2014-04-08 Guided Therapy Systems, Llc Energy-based tissue tightening
US9694212B2 (en) 2004-10-06 2017-07-04 Guided Therapy Systems, Llc Method and system for ultrasound treatment of skin
US8133180B2 (en) 2004-10-06 2012-03-13 Guided Therapy Systems, L.L.C. Method and system for treating cellulite
US7758524B2 (en) 2004-10-06 2010-07-20 Guided Therapy Systems, L.L.C. Method and system for ultra-high frequency ultrasound treatment
ES2643864T3 (es) 2004-10-06 2017-11-24 Guided Therapy Systems, L.L.C. Procedimiento y sistema para el tratamiento de tejidos por ultrasonidos
US11235179B2 (en) 2004-10-06 2022-02-01 Guided Therapy Systems, Llc Energy based skin gland treatment
US9827449B2 (en) 2004-10-06 2017-11-28 Guided Therapy Systems, L.L.C. Systems for treating skin laxity
US11207548B2 (en) 2004-10-07 2021-12-28 Guided Therapy Systems, L.L.C. Ultrasound probe for treating skin laxity
US11724133B2 (en) 2004-10-07 2023-08-15 Guided Therapy Systems, Llc Ultrasound probe for treatment of skin
US7628786B2 (en) 2004-10-13 2009-12-08 Covidien Ag Universal foot switch contact port
US7949407B2 (en) * 2004-11-05 2011-05-24 Asthmatx, Inc. Energy delivery devices and methods
CN101090749B (zh) * 2004-12-27 2013-03-27 皇家飞利浦电子股份有限公司 带有快速安装电池的otc自动外部除纤颤器
KR100674513B1 (ko) * 2004-12-29 2007-01-26 주식회사 메디슨 프로브를 자동으로 활성화시키는 초음파 진단 시스템 및방법
US20110015549A1 (en) * 2005-01-13 2011-01-20 Shimon Eckhouse Method and apparatus for treating a diseased nail
US7909823B2 (en) 2005-01-14 2011-03-22 Covidien Ag Open vessel sealing instrument
US7686804B2 (en) 2005-01-14 2010-03-30 Covidien Ag Vessel sealer and divider with rotating sealer and cutter
US7536225B2 (en) * 2005-01-21 2009-05-19 Ams Research Corporation Endo-pelvic fascia penetrating heating systems and methods for incontinence treatment
US7535247B2 (en) 2005-01-31 2009-05-19 Cascade Microtech, Inc. Interface for testing semiconductors
US7656172B2 (en) 2005-01-31 2010-02-02 Cascade Microtech, Inc. System for testing semiconductors
US20060281763A1 (en) * 2005-03-25 2006-12-14 Axon Jonathan R Carboxamide inhibitors of TGFbeta
WO2006105121A2 (fr) 2005-03-28 2006-10-05 Minnow Medical, Llc Caracterisation de tissu electrique intraluminal et energie rf accordee destinee au traitement selectif d'atherome et d'autres tissus cibles
US9474564B2 (en) 2005-03-31 2016-10-25 Covidien Ag Method and system for compensating for external impedance of an energy carrying component when controlling an electrosurgical generator
US20060235374A1 (en) * 2005-04-15 2006-10-19 Mandel William R In-ice detection for cryotherapy applications
JP4695188B2 (ja) 2005-04-25 2011-06-08 アーデント サウンド， インコーポレイテッド コンピュータ周辺機器の安全性を向上させるための方法および装置
US20060271035A1 (en) * 2005-05-27 2006-11-30 Cardima, Inc. Bipolar tissue dessication system and method
US8588930B2 (en) * 2005-06-07 2013-11-19 Ethicon, Inc. Piezoelectric stimulation device
US7449899B2 (en) 2005-06-08 2008-11-11 Cascade Microtech, Inc. Probe for high frequency signals
JP5080459B2 (ja) 2005-06-13 2012-11-21 カスケード マイクロテック インコーポレイテッド 広帯域能動／受動差動信号プローブ
US20070005049A1 (en) * 2005-06-30 2007-01-04 Comben Richard H Apparatus and Method of Treating Urinary Incontinence by Heating Urethra
US20070016184A1 (en) * 2005-07-14 2007-01-18 Ethicon Endo-Surgery, Inc. Medical-treatment electrode assembly and method for medical treatment
US8950405B2 (en) 2006-05-15 2015-02-10 Tearscience, Inc. Treatment of obstructive disorders of the eye or eyelid
US7981095B2 (en) * 2005-07-18 2011-07-19 Tearscience, Inc. Methods for treating meibomian gland dysfunction employing fluid jet
US7981145B2 (en) 2005-07-18 2011-07-19 Tearscience Inc. Treatment of meibomian glands
US20090043365A1 (en) * 2005-07-18 2009-02-12 Kolis Scientific, Inc. Methods, apparatuses, and systems for reducing intraocular pressure as a means of preventing or treating open-angle glaucoma
WO2013003594A2 (fr) 2011-06-28 2013-01-03 Tearscience, Inc. Procédés et systèmes de traitement de dysfonctionnement de la glande de meibomius à l'aide d'énergie radiofréquence
US7981146B2 (en) * 2006-05-15 2011-07-19 Tearscience Inc. Inner eyelid treatment for treating meibomian gland dysfunction
US20070060988A1 (en) 2005-07-18 2007-03-15 Grenon Stephen M Melting meibomian gland obstructions
US8915253B2 (en) 2005-07-18 2014-12-23 Tearscience, Inc. Method and apparatus for treating gland dysfunction employing heated medium
US20080114423A1 (en) 2006-05-15 2008-05-15 Grenon Stephen M Apparatus for inner eyelid treatment of meibomian gland dysfunction
US7608275B2 (en) 2005-07-22 2009-10-27 The Foundry, Llc Systems and methods for delivery of a therapeutic agent
US20070027511A1 (en) * 2005-08-01 2007-02-01 Ty Fairneny Collagen injection combined with focused ultrasound for the treatment of incontinence
US20070050001A1 (en) * 2005-08-26 2007-03-01 Solarant Medical, Inc. Adjustable open loop control devices and methods
US7879035B2 (en) 2005-09-30 2011-02-01 Covidien Ag Insulating boot for electrosurgical forceps
EP2308406B1 (fr) 2005-09-30 2012-12-12 Covidien AG Manchon isolant pour pince électrochirurgicale
US7922953B2 (en) 2005-09-30 2011-04-12 Covidien Ag Method for manufacturing an end effector assembly
CA2561034C (fr) 2005-09-30 2014-12-09 Sherwood Services Ag Catheter endoscopique flexible avec un effecteur terminal pouvant coaguler et couper les tissus
US7722607B2 (en) 2005-09-30 2010-05-25 Covidien Ag In-line vessel sealer and divider
US20070078502A1 (en) * 2005-10-05 2007-04-05 Thermage, Inc. Method and apparatus for estimating a local impedance factor
US8702691B2 (en) * 2005-10-19 2014-04-22 Thermage, Inc. Treatment apparatus and methods for delivering energy at multiple selectable depths in tissue
US8357095B2 (en) 2005-10-20 2013-01-22 The General Hospital Corporation Non-invasive treatment of fascia
US8734438B2 (en) 2005-10-21 2014-05-27 Covidien Ag Circuit and method for reducing stored energy in an electrosurgical generator
US20070142885A1 (en) * 2005-11-29 2007-06-21 Reliant Technologies, Inc. Method and Apparatus for Micro-Needle Array Electrode Treatment of Tissue
US7947039B2 (en) 2005-12-12 2011-05-24 Covidien Ag Laparoscopic apparatus for performing electrosurgical procedures
CA2574935A1 (fr) 2006-01-24 2007-07-24 Sherwood Services Ag Methode et systeme de commande de sortie d'un generateur radiofrequence d'electrochirurgie presentant un algorithme de flux de commandes base sur l'impedance
US8685016B2 (en) 2006-01-24 2014-04-01 Covidien Ag System and method for tissue sealing
US7513896B2 (en) 2006-01-24 2009-04-07 Covidien Ag Dual synchro-resonant electrosurgical apparatus with bi-directional magnetic coupling
JP5160793B2 (ja) * 2006-01-24 2013-03-13 コヴィディエン・アクチェンゲゼルシャフト 組織シールのためのシステムおよび方法
CA2574934C (fr) 2006-01-24 2015-12-29 Sherwood Services Ag Systeme et methode de monitorage en boucle fermee d'un appareil d'electrochirurgie monopolaire
US8147485B2 (en) 2006-01-24 2012-04-03 Covidien Ag System and method for tissue sealing
US9186200B2 (en) 2006-01-24 2015-11-17 Covidien Ag System and method for tissue sealing
US8216223B2 (en) 2006-01-24 2012-07-10 Covidien Ag System and method for tissue sealing
US7651493B2 (en) 2006-03-03 2010-01-26 Covidien Ag System and method for controlling electrosurgical snares
US8170686B2 (en) * 2006-03-14 2012-05-01 Boston Scientific Scimed, Inc. Heatable sling support for an anatomical location
US8142352B2 (en) 2006-04-03 2012-03-27 Welch Allyn, Inc. Vaginal speculum assembly having portable illuminator
US7651492B2 (en) 2006-04-24 2010-01-26 Covidien Ag Arc based adaptive control system for an electrosurgical unit
US8019435B2 (en) 2006-05-02 2011-09-13 Boston Scientific Scimed, Inc. Control of arterial smooth muscle tone
US8137390B2 (en) 2006-05-15 2012-03-20 Tearscience, Inc. System for providing heat treatment and heat loss reduction for treating meibomian gland dysfunction
US8128674B2 (en) * 2006-05-15 2012-03-06 Tearscience, Inc. System for outer eyelid heat and pressure treatment for treating meibomian gland dysfunction
US7981147B2 (en) * 2006-05-15 2011-07-19 Tearscience, Inc. Outer eyelid heat and pressure treatment for treating meibomian gland dysfunction
US8128673B2 (en) * 2006-05-15 2012-03-06 Tearscience, Inc. System for inner eyelid heat and pressure treatment for treating meibomian gland dysfunction
US7976573B2 (en) * 2006-05-15 2011-07-12 Tearscience, Inc. Inner eyelid heat and pressure treatment for treating meibomian gland dysfunction
US9314369B2 (en) * 2006-05-15 2016-04-19 Tearscience, Inc. System for inner eyelid treatment of meibomian gland dysfunction
US8007524B2 (en) * 2006-05-15 2011-08-30 Tearscience, Inc. Heat treatment and heat loss reduction for treating meibomian gland dysfunction
EP2021846B1 (fr) 2006-05-19 2017-05-03 Koninklijke Philips N.V. Dispositif d'ablation avec profil de puissance d'entrée optimisée
US20140025056A1 (en) * 2006-05-24 2014-01-23 Kambiz Dowlatshahi Image-guided removal and thermal therapy of breast cancer
WO2007140331A2 (fr) 2006-05-25 2007-12-06 Medtronic, Inc. Procédés d'utilisation d'ultrasons focalisés haute densité pour former une zone de tissu soumise à ablation et contenant une pluralité de lésions
WO2007146285A2 (fr) 2006-06-09 2007-12-21 Cascade Microtech, Inc. Sonde différentielle À symétriseur intégré
US7403028B2 (en) 2006-06-12 2008-07-22 Cascade Microtech, Inc. Test structure and probe for differential signals
US7764072B2 (en) 2006-06-12 2010-07-27 Cascade Microtech, Inc. Differential signal probing system
US7723999B2 (en) 2006-06-12 2010-05-25 Cascade Microtech, Inc. Calibration structures for differential signal probing
US7443186B2 (en) 2006-06-12 2008-10-28 Cascade Microtech, Inc. On-wafer test structures for differential signals
WO2008027069A1 (fr) * 2006-08-21 2008-03-06 Tearscience, Inc. Procédé et appareil de traitement du dysfonctionnement de la glande de meibomius au moyen d'un fluide
WO2008039221A1 (fr) * 2006-08-21 2008-04-03 Tearscience, Inc. Fusion d'obstructions de glandes de meibomius
US9566454B2 (en) * 2006-09-18 2017-02-14 Guided Therapy Systems, Llc Method and sysem for non-ablative acne treatment and prevention
US7794457B2 (en) 2006-09-28 2010-09-14 Covidien Ag Transformer for RF voltage sensing
US20080091228A1 (en) * 2006-10-06 2008-04-17 Vascular Technology Inc. Doppler enabled soft tissue dissector
US8273080B2 (en) 2006-10-16 2012-09-25 Syneron Medical Ltd. Methods and devices for treating tissue
US20080281389A1 (en) * 2006-10-16 2008-11-13 Primaeva Medical Inc. Methods and devices for treating tissue
US8133216B2 (en) * 2006-10-16 2012-03-13 Syneron Medical Ltd. Methods and devices for treating tissue
US8007493B2 (en) 2006-10-16 2011-08-30 Syneron Medical Ltd. Methods and devices for treating tissue
US8142426B2 (en) * 2006-10-16 2012-03-27 Syneron Medical Ltd. Methods and devices for treating tissue
JP5312337B2 (ja) 2006-10-18 2013-10-09 べシックス・バスキュラー・インコーポレイテッド 標的組織の選択的な処置のための調節されたｒｆエネルギーおよび電気的な組織の特徴付け
EP2455034B1 (fr) 2006-10-18 2017-07-19 Vessix Vascular, Inc. Système pour induire des effets de température souhaitables sur les tissus corporels
JP5479901B2 (ja) 2006-10-18 2014-04-23 べシックス・バスキュラー・インコーポレイテッド 身体組織に対する所望の温度作用の誘発
US8728140B2 (en) * 2006-11-06 2014-05-20 Stacy Lee Feemster Therapeutic intra-vaginal devices and methods
US9924998B2 (en) 2007-01-12 2018-03-27 Atricure, Inc. Ablation system, clamp and method of use
US20080171905A1 (en) * 2007-01-17 2008-07-17 Ams Research Corporation Transvaginal Delivery of Bulking Masses Adjacent the Urethra to Alleviate Female Incontinence
US10166066B2 (en) * 2007-03-13 2019-01-01 University Of Virginia Patent Foundation Epicardial ablation catheter and method of use
US9211405B2 (en) * 2007-03-22 2015-12-15 University Of Virginia Patent Foundation Electrode catheter for ablation purposes and related method thereof
US9314298B2 (en) * 2007-04-17 2016-04-19 St. Jude Medical, Atrial Fibrillation Divisions, Inc. Vacuum-stabilized ablation system
US9241763B2 (en) 2007-04-19 2016-01-26 Miramar Labs, Inc. Systems, apparatus, methods and procedures for the noninvasive treatment of tissue using microwave energy
US20100114086A1 (en) 2007-04-19 2010-05-06 Deem Mark E Methods, devices, and systems for non-invasive delivery of microwave therapy
EP2837351B1 (fr) * 2007-04-19 2018-05-30 Miramar Labs, Inc. Systèmes pour créer un effet en utilisant une énergie micro-onde sur un tissu spécifié
WO2008131306A1 (fr) 2007-04-19 2008-10-30 The Foundry, Inc. Systèmes et procédés pour créer un effet en utilisant une énergie micro-onde sur un tissu spécifié
JP6100613B2 (ja) * 2007-04-19 2017-03-22 ミラマー ラブズ， インコーポレイテッド 汗の産生を低減するための方法および装置
EP3391844A1 (fr) 2007-04-19 2018-10-24 Miramar Labs, Inc. Appareil pour réduire la production de sueur
US8496653B2 (en) * 2007-04-23 2013-07-30 Boston Scientific Scimed, Inc. Thrombus removal
JP5975600B2 (ja) 2007-05-07 2016-08-24 ガイデッド セラピー システムズ， エル．エル．シー． カプラ部材を使用して音響エネルギーを結合し、かつ焦点に集めるための方法およびシステム
US20150174388A1 (en) 2007-05-07 2015-06-25 Guided Therapy Systems, Llc Methods and Systems for Ultrasound Assisted Delivery of a Medicant to Tissue
JP2010526589A (ja) 2007-05-07 2010-08-05 ガイデッド セラピー システムズ， エル．エル．シー． 音響エネルギーを使用してメディカントを調節するための方法およびシステム
US8777941B2 (en) 2007-05-10 2014-07-15 Covidien Lp Adjustable impedance electrosurgical electrodes
US8845630B2 (en) * 2007-06-15 2014-09-30 Syneron Medical Ltd Devices and methods for percutaneous energy delivery
WO2009009661A1 (fr) * 2007-07-10 2009-01-15 Thermage, Inc. Appareil de traitement et procédés permettant de transmettre une énergie à fréquence élevée sur de vastes zones tissulaires
US7834484B2 (en) * 2007-07-16 2010-11-16 Tyco Healthcare Group Lp Connection cable and method for activating a voltage-controlled generator
US8227681B2 (en) * 2007-07-20 2012-07-24 GM Global Technology Operations LLC Active material apparatus with activating thermoelectric device thereon and method of fabrication
JP5389025B2 (ja) * 2007-08-01 2014-01-15 シネロン メディカル リミテッド コラーゲン増殖刺激のための方法及び装置
US7876114B2 (en) 2007-08-08 2011-01-25 Cascade Microtech, Inc. Differential waveguide probe
US8216220B2 (en) 2007-09-07 2012-07-10 Tyco Healthcare Group Lp System and method for transmission of combined data stream
CA2699782C (fr) * 2007-09-14 2017-04-11 Lazure Technologies, Llc Ablation du cancer de la prostate
US8512332B2 (en) 2007-09-21 2013-08-20 Covidien Lp Real-time arc control in electrosurgical generators
US20090082703A1 (en) * 2007-09-26 2009-03-26 Robert Muratore Method and apparatus for the treatment of tendon abnormalities
US8352026B2 (en) * 2007-10-03 2013-01-08 Ethicon, Inc. Implantable pulse generators and methods for selective nerve stimulation
US8235986B2 (en) * 2007-10-05 2012-08-07 Coaptus Medical Corporation Systems and methods for transeptal cardiac procedures, including tissue penetrating members and associated methods
US20090112205A1 (en) * 2007-10-31 2009-04-30 Primaeva Medical, Inc. Cartridge electrode device
US20100241185A1 (en) 2007-11-09 2010-09-23 University Of Virginia Patent Foundation Steerable epicardial pacing catheter system placed via the subxiphoid process
US20090149930A1 (en) * 2007-12-07 2009-06-11 Thermage, Inc. Apparatus and methods for cooling a treatment apparatus configured to non-invasively deliver electromagnetic energy to a patient's tissue
US20090156958A1 (en) * 2007-12-12 2009-06-18 Mehta Bankim H Devices and methods for percutaneous energy delivery
US8106829B2 (en) * 2007-12-12 2012-01-31 Broadcom Corporation Method and system for an integrated antenna and antenna management
KR101654863B1 (ko) 2007-12-12 2016-09-22 미라마 랩스 인코포레이티드 마이크로파 에너지를 이용하여 조직을 비침투 방식으로 치료하기 위한 시스템, 장치, 방법 및 과정
ES2471971T3 (es) 2007-12-12 2014-06-27 Miramar Labs, Inc. Sistema y aparato para el tratamiento no invasivo de tejido utilizando energía de microondas
WO2009076616A2 (fr) * 2007-12-12 2009-06-18 Rosenblatt Associates, Llc Détection électrique de pénétration de paroi anatomique et délimitation de structures anatomiques pendant une opération chirurgicale
US8998892B2 (en) 2007-12-21 2015-04-07 Atricure, Inc. Ablation device with cooled electrodes and methods of use
US8353907B2 (en) 2007-12-21 2013-01-15 Atricure, Inc. Ablation device with internally cooled electrodes
ES2395454T3 (es) 2008-01-17 2013-02-12 Syneron Medical Ltd. Un aparato para remoción del vello para uso personal y el método de uso del mismo
KR20100115748A (ko) 2008-01-24 2010-10-28 시네론 메디컬 리미티드 지방 조직 치료 장치, 기기, 및 방법
USD617443S1 (en) 2008-02-06 2010-06-08 Tearscience, Inc. Eye treatment goggles
USD613408S1 (en) 2008-02-06 2010-04-06 Tearscience, Inc. Eye treatment head gear
AU2009214608A1 (en) * 2008-02-14 2009-08-20 Robert C. Brown Method for treating stress urinary incontinence and symptomatic pelvic relaxation
US8483831B1 (en) 2008-02-15 2013-07-09 Holaira, Inc. System and method for bronchial dilation
US8515553B2 (en) * 2008-04-28 2013-08-20 Thermage, Inc. Methods and apparatus for predictively controlling the temperature of a coolant delivered to a treatment device
EP2662046B1 (fr) 2008-05-09 2023-03-15 Nuvaira, Inc. Systèmes et ensembles pour le traitement d'un arbre bronchique
US20090287239A1 (en) * 2008-05-16 2009-11-19 Ams Research Corporation Tissue Bulking Device and Method
EP3058875B1 (fr) 2008-06-06 2022-08-17 Ulthera, Inc. Système pour traitement cosmétique et imagerie
US12102473B2 (en) 2008-06-06 2024-10-01 Ulthera, Inc. Systems for ultrasound treatment
US8226639B2 (en) 2008-06-10 2012-07-24 Tyco Healthcare Group Lp System and method for output control of electrosurgical generator
AU2009257370B2 (en) * 2008-06-14 2015-01-22 Auris Health, Inc. System and method for delivering energy to tissue
US8121704B2 (en) * 2008-06-19 2012-02-21 Thermage, Inc. Leakage-resistant tissue treatment apparatus and methods of using same
US8285392B2 (en) * 2008-06-19 2012-10-09 Thermage, Inc. Leakage-resistant tissue treatment apparatus and methods of using such tissue treatment apparatus
US8795264B2 (en) * 2008-07-01 2014-08-05 Ralph Zipper Method for decreasing the size and/or changing the shape of pelvic tissues
DE102008050635A1 (de) * 2008-10-07 2010-04-15 Erbe Elektromedizin Gmbh Verfahren und Vorrichtung zur Regelung einer gekühlten RF-Ablationssonde
US8892210B2 (en) 2008-07-02 2014-11-18 Niveus Medical, Inc. Devices, systems, and methods for automated optimization of energy delivery
US9314293B2 (en) 2008-07-16 2016-04-19 Syneron Medical Ltd RF electrode for aesthetic and body shaping devices and method of using same
US20100017750A1 (en) 2008-07-16 2010-01-21 Avner Rosenberg User interface
US9149386B2 (en) 2008-08-19 2015-10-06 Niveus Medical, Inc. Devices and systems for stimulation of tissues
US8403924B2 (en) * 2008-09-03 2013-03-26 Vivant Medical, Inc. Shielding for an isolation apparatus used in a microwave generator
EP2323597B1 (fr) * 2008-09-11 2014-06-25 Syneron Medical Ltd. Appareil de traitement de la peau saine pour une utilisation personnelle
MX2011002987A (es) 2008-09-21 2011-07-20 Syneron Medical Ltd Un metodo y aparato para el tratamiento personal de la piel.
EP2341839B1 (fr) * 2008-09-22 2015-10-21 Vessix Vascular, Inc. Système de traitements vasculaires par ultrasons
US10028753B2 (en) 2008-09-26 2018-07-24 Relievant Medsystems, Inc. Spine treatment kits
CA2737374C (fr) 2008-09-26 2017-03-28 Relievant Medsystems, Inc. Systemes et procedes pour piloter un instrument a travers un os
US8346370B2 (en) * 2008-09-30 2013-01-01 Vivant Medical, Inc. Delivered energy generator for microwave ablation
US8287527B2 (en) * 2008-09-30 2012-10-16 Vivant Medical, Inc. Microwave system calibration apparatus and method of use
US8242782B2 (en) * 2008-09-30 2012-08-14 Vivant Medical, Inc. Microwave ablation generator control system
US20100082083A1 (en) * 2008-09-30 2010-04-01 Brannan Joseph D Microwave system tuner
US8174267B2 (en) * 2008-09-30 2012-05-08 Vivant Medical, Inc. Intermittent microwave energy delivery system
US8248075B2 (en) * 2008-09-30 2012-08-21 Vivant Medical, Inc. System, apparatus and method for dissipating standing wave in a microwave delivery system
US8180433B2 (en) * 2008-09-30 2012-05-15 Vivant Medical, Inc. Microwave system calibration apparatus, system and method of use
US8142473B2 (en) 2008-10-03 2012-03-27 Tyco Healthcare Group Lp Method of transferring rotational motion in an articulating surgical instrument
US7888957B2 (en) 2008-10-06 2011-02-15 Cascade Microtech, Inc. Probing apparatus with impedance optimized interface
US8016827B2 (en) 2008-10-09 2011-09-13 Tyco Healthcare Group Lp Apparatus, system, and method for performing an electrosurgical procedure
US8386010B2 (en) * 2008-10-23 2013-02-26 Covidien Lp Surgical tissue monitoring system
EP2355737B1 (fr) 2008-11-17 2021-08-11 Boston Scientific Scimed, Inc. Accumulation sélective d énergie sans connaissance de la topographie tissulaire
US8410806B2 (en) 2008-11-21 2013-04-02 Cascade Microtech, Inc. Replaceable coupon for a probing apparatus
US8319503B2 (en) 2008-11-24 2012-11-27 Cascade Microtech, Inc. Test apparatus for measuring a characteristic of a device under test
US8357150B2 (en) * 2009-07-20 2013-01-22 Syneron Medical Ltd. Method and apparatus for fractional skin treatment
US10668285B2 (en) 2008-12-05 2020-06-02 Spr Therapeutics, Inc. Systems and methods to place one or more leads in tissue to electrically stimulate nerves to treat pain
US9895530B2 (en) 2008-12-05 2018-02-20 Spr Therapeutics, Inc. Systems and methods to place one or more leads in tissue to electrically stimulate nerves of passage to treat pain
EP2382010A4 (fr) 2008-12-24 2014-05-14 Guided Therapy Systems Llc Procédés et systèmes pour réduire les graisses et/ou traiter la cellulite
EP2376011B1 (fr) 2009-01-09 2019-07-03 ReCor Medical, Inc. Appareils de traitement de l'insuffisance de la valve mitrale
US8262652B2 (en) 2009-01-12 2012-09-11 Tyco Healthcare Group Lp Imaginary impedance process monitoring and intelligent shut-off
US8114122B2 (en) 2009-01-13 2012-02-14 Tyco Healthcare Group Lp Apparatus, system, and method for performing an electrosurgical procedure
US9254168B2 (en) 2009-02-02 2016-02-09 Medtronic Advanced Energy Llc Electro-thermotherapy of tissue using penetrating microelectrode array
US20100211060A1 (en) * 2009-02-13 2010-08-19 Cutera, Inc. Radio frequency treatment of subcutaneous fat
US20100211055A1 (en) * 2009-02-18 2010-08-19 Shimon Eckhouse Method for body toning and an integrated data management system for the same
US8606366B2 (en) 2009-02-18 2013-12-10 Syneron Medical Ltd. Skin treatment apparatus for personal use and method for using same
WO2010096776A2 (fr) * 2009-02-20 2010-08-26 Niveus Medical, Inc. Systèmes et procédés de stimulation musculaire électrique à l'aide d'un champ de guidage d'énergie
ES2461619T3 (es) 2009-02-25 2014-05-20 Syneron Medical Ltd. Rejuvenecimiento eléctrico de la piel
US20100217254A1 (en) * 2009-02-25 2010-08-26 Primaeva Medical, Inc. Methods for applying energy to tissue using isolated energy sources
US20110245587A1 (en) * 2010-04-05 2011-10-06 Julie Ann Reil Method for correction of female urinary incontinence and skin reduction
US8961577B2 (en) 2009-04-02 2015-02-24 Julie Ann Reil Correction of female urinary incontinence and skin reduction
US8632534B2 (en) 2009-04-03 2014-01-21 Angiodynamics, Inc. Irreversible electroporation (IRE) for congestive obstructive pulmonary disease (COPD)
US8187273B2 (en) 2009-05-07 2012-05-29 Tyco Healthcare Group Lp Apparatus, system, and method for performing an electrosurgical procedure
US8551096B2 (en) 2009-05-13 2013-10-08 Boston Scientific Scimed, Inc. Directional delivery of energy and bioactives
US8483832B2 (en) * 2009-05-20 2013-07-09 ElectroCore, LLC Systems and methods for selectively applying electrical energy to tissue
WO2010138919A2 (fr) 2009-05-28 2010-12-02 Angiodynamics, Inc. Système et méthode de synchronisation de l'apport d'énergie et du rythme cardiaque
US9895189B2 (en) 2009-06-19 2018-02-20 Angiodynamics, Inc. Methods of sterilization and treating infection using irreversible electroporation
US8246618B2 (en) 2009-07-08 2012-08-21 Tyco Healthcare Group Lp Electrosurgical jaws with offset knife
RU2012107673A (ru) 2009-08-04 2013-09-10 Поллоген Лтд. Косметическое омоложение кожи
US9089315B1 (en) * 2009-09-02 2015-07-28 The Regents Of The University Of California Methods and devices for adjunctive local hypothermia
JP2013503723A (ja) 2009-09-08 2013-02-04 サリエント・サージカル・テクノロジーズ・インコーポレーテッド 電気手術デバイスのためのカートリッジアセンブリ、電気手術ユニット、およびそれらの使用方法
US9642534B2 (en) 2009-09-11 2017-05-09 University Of Virginia Patent Foundation Systems and methods for determining location of an access needle in a subject
US8133254B2 (en) 2009-09-18 2012-03-13 Tyco Healthcare Group Lp In vivo attachable and detachable end effector assembly and laparoscopic surgical instrument and methods therefor
US8112871B2 (en) 2009-09-28 2012-02-14 Tyco Healthcare Group Lp Method for manufacturing electrosurgical seal plates
USD638128S1 (en) 2009-10-06 2011-05-17 Tearscience, Inc. Ocular device design
AU2010315396B2 (en) 2009-10-27 2016-05-05 Nuvaira, Inc Delivery devices with coolable energy emitting assemblies
EP3132828B1 (fr) 2009-10-30 2017-10-11 ReCor Medical, Inc. Appareil pour le traitement de l'hypertension par dénervation rénale à ultrasons percutanée
US20110112520A1 (en) * 2009-11-11 2011-05-12 Invasix Corporation Method and device for fat treatment
CA2780608C (fr) 2009-11-11 2019-02-26 Innovative Pulmonary Solutions, Inc. Systemes, appareils et procedes pour traiter un tissu et controler une stenose
WO2011060056A2 (fr) 2009-11-11 2011-05-19 Niveus Mediacl, Inc. Dispositif d'activation de muscle synergique
US8911439B2 (en) 2009-11-11 2014-12-16 Holaira, Inc. Non-invasive and minimally invasive denervation methods and systems for performing the same
WO2011058565A2 (fr) 2009-11-16 2011-05-19 Pollogen Ltd. Retrait de graisse non invasif
US11590346B2 (en) 2009-11-16 2023-02-28 Pollogen Ltd. Apparatus and method for cosmetic treatment of human mucosal tissue
US8715186B2 (en) 2009-11-24 2014-05-06 Guided Therapy Systems, Llc Methods and systems for generating thermal bubbles for improved ultrasound imaging and therapy
KR101784536B1 (ko) 2009-12-06 2017-11-06 시네론 메디컬 리미티드 개인용 피부 미용 치료 장치 및 방법
DE102009059196A1 (de) * 2009-12-17 2011-06-22 Aesculap AG, 78532 Chirurgisches System zum Verbinden von Körpergewebe
DE102009059192A1 (de) * 2009-12-17 2011-06-22 Aesculap AG, 78532 Chirurgisches System und Steuerungsverfahren für ein chirurgisches Instrument und Verfahren zum Verbinden von Körpergewebeteilen
US8512325B2 (en) * 2010-02-26 2013-08-20 Covidien Lp Frequency shifting multi mode ultrasonic dissector
WO2011112991A1 (fr) 2010-03-11 2011-09-15 Salient Surgical Technologies, Inc. Instrument tranchant électrochirurgical bipolaire comprenant une électrode de référence de contact indépendante de la position
CA2795564C (fr) * 2010-04-06 2021-06-15 Innovative Pulmonary Solutions, Inc. Systeme et methode de traitement pulmonaire
KR20130108067A (ko) 2010-04-09 2013-10-02 베식스 바스큘라 인코포레이티드 조직 치료를 위한 발전 및 제어 장치
US9192790B2 (en) 2010-04-14 2015-11-24 Boston Scientific Scimed, Inc. Focused ultrasonic renal denervation
US9242122B2 (en) 2010-05-14 2016-01-26 Liat Tsoref Reflectance-facilitated ultrasound treatment and monitoring
US8473067B2 (en) 2010-06-11 2013-06-25 Boston Scientific Scimed, Inc. Renal denervation and stimulation employing wireless vascular energy transfer arrangement
US8920417B2 (en) 2010-06-30 2014-12-30 Medtronic Advanced Energy Llc Electrosurgical devices and methods of use thereof
US9358365B2 (en) 2010-07-30 2016-06-07 Boston Scientific Scimed, Inc. Precision electrode movement control for renal nerve ablation
US9408661B2 (en) 2010-07-30 2016-08-09 Patrick A. Haverkost RF electrodes on multiple flexible wires for renal nerve ablation
US9084609B2 (en) 2010-07-30 2015-07-21 Boston Scientific Scime, Inc. Spiral balloon catheter for renal nerve ablation
US9463062B2 (en) 2010-07-30 2016-10-11 Boston Scientific Scimed, Inc. Cooled conductive balloon RF catheter for renal nerve ablation
US9155589B2 (en) * 2010-07-30 2015-10-13 Boston Scientific Scimed, Inc. Sequential activation RF electrode set for renal nerve ablation
US9504446B2 (en) 2010-08-02 2016-11-29 Guided Therapy Systems, Llc Systems and methods for coupling an ultrasound source to tissue
US10183182B2 (en) 2010-08-02 2019-01-22 Guided Therapy Systems, Llc Methods and systems for treating plantar fascia
US9700368B2 (en) 2010-10-13 2017-07-11 Angiodynamics, Inc. System and method for electrically ablating tissue of a patient
TWI556849B (zh) 2010-10-21 2016-11-11 美敦力阿福盧森堡公司 用於腎臟神經協調的導管裝置
CN106377312B (zh) 2010-10-25 2019-12-10 美敦力Af卢森堡有限责任公司 用于肾神经调节的微波导管设备、系统和方法
US8974451B2 (en) 2010-10-25 2015-03-10 Boston Scientific Scimed, Inc. Renal nerve ablation using conductive fluid jet and RF energy
US9023040B2 (en) 2010-10-26 2015-05-05 Medtronic Advanced Energy Llc Electrosurgical cutting devices
US9220558B2 (en) 2010-10-27 2015-12-29 Boston Scientific Scimed, Inc. RF renal denervation catheter with multiple independent electrodes
US8857438B2 (en) 2010-11-08 2014-10-14 Ulthera, Inc. Devices and methods for acoustic shielding
US8788047B2 (en) 2010-11-11 2014-07-22 Spr Therapeutics, Llc Systems and methods for the treatment of pain through neural fiber stimulation
US8788046B2 (en) 2010-11-11 2014-07-22 Spr Therapeutics, Llc Systems and methods for the treatment of pain through neural fiber stimulation
US8788048B2 (en) 2010-11-11 2014-07-22 Spr Therapeutics, Llc Systems and methods for the treatment of pain through neural fiber stimulation
US9028485B2 (en) 2010-11-15 2015-05-12 Boston Scientific Scimed, Inc. Self-expanding cooling electrode for renal nerve ablation
US9668811B2 (en) 2010-11-16 2017-06-06 Boston Scientific Scimed, Inc. Minimally invasive access for renal nerve ablation
US9089350B2 (en) 2010-11-16 2015-07-28 Boston Scientific Scimed, Inc. Renal denervation catheter with RF electrode and integral contrast dye injection arrangement
US9326751B2 (en) 2010-11-17 2016-05-03 Boston Scientific Scimed, Inc. Catheter guidance of external energy for renal denervation
US9060761B2 (en) 2010-11-18 2015-06-23 Boston Scientific Scime, Inc. Catheter-focused magnetic field induced renal nerve ablation
US9023034B2 (en) 2010-11-22 2015-05-05 Boston Scientific Scimed, Inc. Renal ablation electrode with force-activatable conduction apparatus
US9192435B2 (en) 2010-11-22 2015-11-24 Boston Scientific Scimed, Inc. Renal denervation catheter with cooled RF electrode
US9204922B2 (en) 2010-12-01 2015-12-08 Enable Urology, Llc Method and apparatus for remodeling/profiling a tissue lumen, particularly in the urethral lumen in the prostate gland
US20120157993A1 (en) 2010-12-15 2012-06-21 Jenson Mark L Bipolar Off-Wall Electrode Device for Renal Nerve Ablation
US9113940B2 (en) 2011-01-14 2015-08-25 Covidien Lp Trigger lockout and kickback mechanism for surgical instruments
WO2012100095A1 (fr) 2011-01-19 2012-07-26 Boston Scientific Scimed, Inc. Cathéter à grande électrode compatible avec un guide pour ablation de nerf rénal à lésion artérielle réduite
US8317703B2 (en) * 2011-02-17 2012-11-27 Vivant Medical, Inc. Energy-delivery device including ultrasound transducer array and phased antenna array, and methods of adjusting an ablation field radiating into tissue using same
US8376948B2 (en) 2011-02-17 2013-02-19 Vivant Medical, Inc. Energy-delivery device including ultrasound transducer array and phased antenna array
US9427281B2 (en) 2011-03-11 2016-08-30 Medtronic Advanced Energy Llc Bronchoscope-compatible catheter provided with electrosurgical device
EP2699316B1 (fr) * 2011-04-05 2016-06-01 INSERM - Institut National de la Santé et de la Recherche Médicale Dispositif transoesophagien utilisant des ultra-sons focalisés de haute intensité pour une ablation thermique cardiaque
CN103517731B (zh) 2011-04-08 2016-08-31 柯惠有限合伙公司 用于去除肾交感神经和离子电渗式药物传递的离子电渗式药物传递系统和方法
EP2701623B1 (fr) 2011-04-25 2016-08-17 Medtronic Ardian Luxembourg S.à.r.l. Appareil relatifs au déploiement restreint de ballonnets cryogéniques pour une ablation cryogénique limitée de parois de vaisseaux
EP2739357B1 (fr) 2011-07-10 2023-09-06 Guided Therapy Systems, L.L.C. Système pour améliorer l'aspect extérieur de la peau en utilisant les ultrasons comme source d'énergie
US9011337B2 (en) 2011-07-11 2015-04-21 Guided Therapy Systems, Llc Systems and methods for monitoring and controlling ultrasound power output and stability
US9028482B2 (en) 2011-07-19 2015-05-12 Covidien Lp Microwave and RF ablation system and related method for dynamic impedance matching
US8968297B2 (en) 2011-07-19 2015-03-03 Covidien Lp Microwave and RF ablation system and related method for dynamic impedance matching
US9192422B2 (en) 2011-07-19 2015-11-24 Covidien Lp System and method of matching impedances of an electrosurgical generator and/or a microwave generator
EP2734259B1 (fr) 2011-07-20 2016-11-23 Boston Scientific Scimed, Inc. Dispositif percutanés de visualisation, de ciblage et d'ablation de nerfs
CN103813829B (zh) 2011-07-22 2016-05-18 波士顿科学西美德公司 具有可定位于螺旋引导件中的神经调制元件的神经调制系统
CA2843183A1 (fr) 2011-07-26 2013-01-31 Amphora Medical, Inc. Appareils et procedes de modulation du tissu nerveux pelvien
US9314301B2 (en) 2011-08-01 2016-04-19 Miramar Labs, Inc. Applicator and tissue interface module for dermatological device
US8706258B2 (en) 2011-08-08 2014-04-22 Medamp Electronics, Llc Method and apparatus for treating cancer
US9486625B2 (en) 2011-08-08 2016-11-08 Medamp Electronics, Llc Method for treating benign prostate hyperplasia
US20130066308A1 (en) * 2011-08-31 2013-03-14 Jaime Landman Ablation-based therapy for bladder pathologies
US9339339B2 (en) 2011-09-16 2016-05-17 Boston Scientific Scimed, Inc. Medical device and method for conducting a surgery through a body opening
US9078665B2 (en) 2011-09-28 2015-07-14 Angiodynamics, Inc. Multiple treatment zone ablation probe
US9750565B2 (en) 2011-09-30 2017-09-05 Medtronic Advanced Energy Llc Electrosurgical balloons
EP2765942B1 (fr) 2011-10-10 2016-02-24 Boston Scientific Scimed, Inc. Dispositifs médicaux comprenant des électrodes d'ablation
WO2013055815A1 (fr) 2011-10-11 2013-04-18 Boston Scientific Scimed, Inc. Dispositif d'électrode hors paroi pour une modulation nerveuse
US9420955B2 (en) 2011-10-11 2016-08-23 Boston Scientific Scimed, Inc. Intravascular temperature monitoring system and method
US9364284B2 (en) 2011-10-12 2016-06-14 Boston Scientific Scimed, Inc. Method of making an off-wall spacer cage
WO2013058962A1 (fr) 2011-10-18 2013-04-25 Boston Scientific Scimed, Inc. Dispositifs médicaux pouvant être déviés
WO2013059202A1 (fr) 2011-10-18 2013-04-25 Boston Scientific Scimed, Inc. Cathéter à ballonnet à traversée intégrée
US8968308B2 (en) 2011-10-20 2015-03-03 Covidien Lp Multi-circuit seal plates
WO2013070724A1 (fr) 2011-11-08 2013-05-16 Boston Scientific Scimed, Inc. Ablation ostiale du nerf rénal
US9119600B2 (en) 2011-11-15 2015-09-01 Boston Scientific Scimed, Inc. Device and methods for renal nerve modulation monitoring
US9119632B2 (en) 2011-11-21 2015-09-01 Boston Scientific Scimed, Inc. Deflectable renal nerve ablation catheter
EP2782512A4 (fr) * 2011-11-24 2015-08-26 Syneron Medical Ltd Appareil de traitement de la peau sans risque à usage personnel et son procédé d'utilisation
US9131980B2 (en) 2011-12-19 2015-09-15 Medtronic Advanced Energy Llc Electrosurgical devices
US9265969B2 (en) 2011-12-21 2016-02-23 Cardiac Pacemakers, Inc. Methods for modulating cell function
EP2793689B1 (fr) 2011-12-23 2023-05-10 Vessix Vascular, Inc. Systèmes pour remodeler des tissus et
CN104135958B (zh) 2011-12-28 2017-05-03 波士顿科学西美德公司 用有聚合物消融元件的新消融导管调变神经的装置和方法
US9050106B2 (en) 2011-12-29 2015-06-09 Boston Scientific Scimed, Inc. Off-wall electrode device and methods for nerve modulation
WO2013101772A1 (fr) 2011-12-30 2013-07-04 Relievant Medsystems, Inc. Systèmes et méthodes de traitement de douleur dorsale
USD680220S1 (en) 2012-01-12 2013-04-16 Coviden IP Slider handle for laparoscopic device
US10076383B2 (en) 2012-01-25 2018-09-18 Covidien Lp Electrosurgical device having a multiplexer
US9414881B2 (en) 2012-02-08 2016-08-16 Angiodynamics, Inc. System and method for increasing a target zone for electrical ablation
US9707414B2 (en) 2012-02-14 2017-07-18 Rainbow Medical Ltd. Reflectance-facilitated ultrasound treatment and monitoring
JP5963505B2 (ja) * 2012-04-02 2016-08-03 オリンパス株式会社 超音波治療装置
US8403927B1 (en) 2012-04-05 2013-03-26 William Bruce Shingleton Vasectomy devices and methods
JP6066259B2 (ja) * 2012-04-06 2017-01-25 学校法人東京理科大学 体内局所加温装置
US9263663B2 (en) 2012-04-13 2016-02-16 Ardent Sound, Inc. Method of making thick film transducer arrays
US9883906B2 (en) 2012-04-22 2018-02-06 Newuro, B.V. Bladder tissue modification for overactive bladder disorders
US10610294B2 (en) 2012-04-22 2020-04-07 Newuro, B.V. Devices and methods for transurethral bladder partitioning
US10660703B2 (en) 2012-05-08 2020-05-26 Boston Scientific Scimed, Inc. Renal nerve modulation devices
EP3639781B1 (fr) * 2012-05-18 2023-12-20 Nuvaira, Inc. Systèmes et appareils de traitement de tissus et de régulation de la sténose
US10842670B2 (en) 2012-08-22 2020-11-24 Johnson & Johnson Vision Care, Inc. Apparatuses and methods for diagnosing and/or treating lipid transport deficiency in ocular tear films, and related components and devices
CN104540465A (zh) 2012-08-24 2015-04-22 波士顿科学西美德公司 带有含单独微孔隙区域的球囊的血管内导管
US10588691B2 (en) 2012-09-12 2020-03-17 Relievant Medsystems, Inc. Radiofrequency ablation of tissue within a vertebral body
CN104780859B (zh) 2012-09-17 2017-07-25 波士顿科学西美德公司 用于肾神经调节的自定位电极系统及方法
US10549127B2 (en) 2012-09-21 2020-02-04 Boston Scientific Scimed, Inc. Self-cooling ultrasound ablation catheter
WO2014047411A1 (fr) 2012-09-21 2014-03-27 Boston Scientific Scimed, Inc. Système de modulation des nerfs et blocage des nerfs par gradient thermique inoffensif
US9510802B2 (en) 2012-09-21 2016-12-06 Guided Therapy Systems, Llc Reflective ultrasound technology for dermatological treatments
US9687290B2 (en) 2012-10-02 2017-06-27 Covidien Lp Energy-based medical devices
US10835305B2 (en) 2012-10-10 2020-11-17 Boston Scientific Scimed, Inc. Renal nerve modulation devices and methods
EP3598952A3 (fr) 2012-11-05 2020-04-15 Relievant Medsystems, Inc. Systèmes et procédés pour créer des chemins incurvés à travers des os et moduler des nerfs dans l'os
US9398933B2 (en) 2012-12-27 2016-07-26 Holaira, Inc. Methods for improving drug efficacy including a combination of drug administration and nerve modulation
US20160008635A1 (en) * 2013-02-04 2016-01-14 Everette C. Burdette Catheter-based ultrasound transducers
CN104027893B (zh) 2013-03-08 2021-08-31 奥赛拉公司 用于多焦点超声治疗的装置和方法
WO2014163987A1 (fr) 2013-03-11 2014-10-09 Boston Scientific Scimed, Inc. Dispositifs médicaux pour la modulation des nerfs
WO2014143571A1 (fr) 2013-03-11 2014-09-18 Boston Scientific Scimed, Inc. Dispositifs médicaux pour moduler des nerfs
US11147990B2 (en) 2013-03-12 2021-10-19 Acoustic Medsystems, Inc. Ultrasound therapy catheter with multi-chambered balloons for transluminal longitudinal positioning
US9808311B2 (en) 2013-03-13 2017-11-07 Boston Scientific Scimed, Inc. Deflectable medical devices
WO2014153149A1 (fr) 2013-03-14 2014-09-25 Ellman International, Inc. Systèmes et procédés électrochirurgicaux
CN105188848B (zh) 2013-03-14 2019-12-10 瑞蔻医药有限公司 基于超声波的神经调制系统
EP2971232A1 (fr) 2013-03-14 2016-01-20 ReCor Medical, Inc. Procédés de placage ou de revêtement de capteurs ultrasonores
EP2967711B1 (fr) 2013-03-15 2020-05-06 Cynosure, LLC Instruments électrochirurgicales dotés de multiples modes d'opération
WO2014150553A1 (fr) 2013-03-15 2014-09-25 Boston Scientific Scimed, Inc. Procédés et appareils pour remodéliser un tissu de ou adjacent à un passage corporel
AU2014237950B2 (en) 2013-03-15 2017-04-13 Boston Scientific Scimed, Inc. Control unit for use with electrode pads and a method for estimating an electrical leakage
US10561862B2 (en) 2013-03-15 2020-02-18 Guided Therapy Systems, Llc Ultrasound treatment device and methods of use
US10265122B2 (en) 2013-03-15 2019-04-23 Boston Scientific Scimed, Inc. Nerve ablation devices and related methods of use
US10092449B2 (en) 2013-04-30 2018-10-09 Tear Film Innovations, Inc. Systems and methods for the treatment of eye conditions
US9763827B2 (en) 2013-04-30 2017-09-19 Tear Film Innovations, Inc. Systems and methods for the treatment of eye conditions
CA2913346A1 (fr) * 2013-06-05 2014-12-11 Metavention, Inc. Modulation de fibres nerveuses ciblees
JP2016523147A (ja) 2013-06-21 2016-08-08 ボストン サイエンティフィック サイムド，インコーポレイテッドＢｏｓｔｏｎ Ｓｃｉｅｎｔｉｆｉｃ Ｓｃｉｍｅｄ，Ｉｎｃ． 同乗型電極支持体を備えた腎除神経バルーンカテーテル
WO2014201511A1 (fr) * 2013-06-21 2014-12-24 Gary David Housley Procédé et appareil pour l'électroporation en champ proche
WO2014205399A1 (fr) 2013-06-21 2014-12-24 Boston Scientific Scimed, Inc. Dispositifs médicaux pour une ablation de nerf rénal ayant des tiges rotatives
US9707036B2 (en) 2013-06-25 2017-07-18 Boston Scientific Scimed, Inc. Devices and methods for nerve modulation using localized indifferent electrodes
WO2015002787A1 (fr) 2013-07-01 2015-01-08 Boston Scientific Scimed, Inc. Dispositifs médicaux pour une ablation de nerf rénal
WO2015006480A1 (fr) 2013-07-11 2015-01-15 Boston Scientific Scimed, Inc. Dispositifs et procédés de modulation nerveuse
US10413357B2 (en) 2013-07-11 2019-09-17 Boston Scientific Scimed, Inc. Medical device with stretchable electrode assemblies
WO2015010074A1 (fr) 2013-07-19 2015-01-22 Boston Scientific Scimed, Inc. Ballonnet de dénervation rénale à électrode bipolaire en spirale
CN105392435B (zh) 2013-07-22 2018-11-09 波士顿科学国际有限公司 具有扭绞球囊的肾神经消融导管
WO2015013205A1 (fr) 2013-07-22 2015-01-29 Boston Scientific Scimed, Inc. Dispositifs médicaux pour l'ablation de nerfs rénaux
WO2015013502A2 (fr) 2013-07-24 2015-01-29 Miramar Labs, Inc. Appareil et méthodes de traitement d'un tissu avec de l'énergie micro-onde
US9872719B2 (en) 2013-07-24 2018-01-23 Covidien Lp Systems and methods for generating electrosurgical energy using a multistage power converter
US9655670B2 (en) 2013-07-29 2017-05-23 Covidien Lp Systems and methods for measuring tissue impedance through an electrosurgical cable
US9724151B2 (en) 2013-08-08 2017-08-08 Relievant Medsystems, Inc. Modulating nerves within bone using bone fasteners
US10213248B2 (en) 2013-08-21 2019-02-26 Biosense Webster (Israel) Ltd. Adaptive electrode for bi-polar ablation
EP3035879A1 (fr) 2013-08-22 2016-06-29 Boston Scientific Scimed, Inc. Circuit flexible ayant une adhérence améliorée à un ballon de modulation de nerf rénal
US9895194B2 (en) 2013-09-04 2018-02-20 Boston Scientific Scimed, Inc. Radio frequency (RF) balloon catheter having flushing and cooling capability
CN105530885B (zh) 2013-09-13 2020-09-22 波士顿科学国际有限公司 具有气相沉积覆盖层的消融球囊
WO2015041170A1 (fr) * 2013-09-20 2015-03-26 テルモ株式会社 Outil d'introduction et procédé pour introduire l'outil d'introduction
WO2015057521A1 (fr) 2013-10-14 2015-04-23 Boston Scientific Scimed, Inc. Cathéter de cartographie cardiaque à haute résolution comportant un ensemble d'électrodes
US11246654B2 (en) 2013-10-14 2022-02-15 Boston Scientific Scimed, Inc. Flexible renal nerve ablation devices and related methods of use and manufacture
US9962223B2 (en) 2013-10-15 2018-05-08 Boston Scientific Scimed, Inc. Medical device balloon
US9770606B2 (en) 2013-10-15 2017-09-26 Boston Scientific Scimed, Inc. Ultrasound ablation catheter with cooling infusion and centering basket
CN105636538B (zh) 2013-10-18 2019-01-15 波士顿科学国际有限公司 具有柔性导线的球囊导管及其使用和制造的相关方法
WO2015061457A1 (fr) 2013-10-25 2015-04-30 Boston Scientific Scimed, Inc. Thermocouple intégré dans un circuit souple d'énervation
WO2015103617A1 (fr) 2014-01-06 2015-07-09 Boston Scientific Scimed, Inc. Ensemble circuit souple résistant aux déchirures
EP3424453A1 (fr) 2014-02-04 2019-01-09 Boston Scientific Scimed, Inc. Placement alternatif de capteurs thermiques sur une électrode bipolaire
US10555746B2 (en) 2014-02-04 2020-02-11 Hologic, Inc. Devices and methods for treating conditions caused by affarent nerve signals
US11000679B2 (en) 2014-02-04 2021-05-11 Boston Scientific Scimed, Inc. Balloon protection and rewrapping devices and related methods of use
PL3017845T3 (pl) 2014-03-18 2022-01-31 Hironic Co., Ltd. Urządzenie operacyjne przy użyciu skupionej wiązki fal ultradźwiękowych o dużym natężeniu
CA3177417A1 (fr) 2014-04-18 2015-10-22 Ulthera, Inc. Traitement par ultrasons emis par un transducteur a bandes
US10709490B2 (en) 2014-05-07 2020-07-14 Medtronic Ardian Luxembourg S.A.R.L. Catheter assemblies comprising a direct heating element for renal neuromodulation and associated systems and methods
AT516099B1 (de) * 2014-07-31 2016-07-15 Smartbow Gmbh Vorrichtung für die Temperaturmessung im Anus oder in der Vagina eines Tieres
US12114911B2 (en) 2014-08-28 2024-10-15 Angiodynamics, Inc. System and method for ablating a tissue site by electroporation with real-time pulse monitoring
WO2016081611A1 (fr) 2014-11-19 2016-05-26 Advanced Cardiac Therapeutics, Inc. Cartographie haute résolution de tissus avec stimulation cardiaque
WO2016081650A1 (fr) 2014-11-19 2016-05-26 Advanced Cardiac Therapeutics, Inc. Dispositifs d'ablation, systèmes et procédés d'utilisation d'ensemble électrode à haute résolution
AU2015350007A1 (en) 2014-11-19 2017-06-29 Epix Therapeutics, Inc. Systems and methods for high-resolution mapping of tissue
JP6682539B2 (ja) * 2014-12-19 2020-04-15 ハイロニック コーポレーション リミテッドＨｉｒｏｎｉｃ Ｃｏ．，Ｌｔｄ． 集束超音波施術装置
US9636164B2 (en) 2015-03-25 2017-05-02 Advanced Cardiac Therapeutics, Inc. Contact sensing systems and methods
DE102015108469A1 (de) * 2015-05-28 2016-12-01 Wellcomet Gmbh Verfahren und Vorrichtung zur Behandlung von Gewebe mittels zumindest einer zumindest bipolaren Elektrode
US11389227B2 (en) 2015-08-20 2022-07-19 Medtronic Advanced Energy Llc Electrosurgical device with multivariate control
US11051875B2 (en) 2015-08-24 2021-07-06 Medtronic Advanced Energy Llc Multipurpose electrosurgical device
WO2017031712A1 (fr) 2015-08-26 2017-03-02 Covidien Lp Ensembles effecteurs terminaux électrochirurgicaux et pinces électrochirurgicales conçues pour réduire l'étalement thermique
WO2017049216A1 (fr) * 2015-09-16 2017-03-23 Viveve Medical, Inc. Procédés et systèmes de traitement de l'incontinence urinaire à l'effort
US10327812B2 (en) 2015-11-04 2019-06-25 Rainbow Medical Ltd. Pericardial access device
US10213250B2 (en) 2015-11-05 2019-02-26 Covidien Lp Deployment and safety mechanisms for surgical instruments
CN108366828B (zh) * 2015-12-16 2022-04-15 保隆恩有限公司 用于人体粘膜组织的美容治疗的装置和方法
KR102707101B1 (ko) 2016-01-18 2024-09-13 얼테라, 인크 환형 초음파 어레이가 가요성 인쇄 회로 기판에 지엽적으로 전기적으로 연결된 컴팩트한 초음파 디바이스 및 그 조립 방법
SG11201807618QA (en) 2016-03-15 2018-10-30 Epix Therapeutics Inc Improved devices, systems and methods for irrigated ablation
US10974063B2 (en) 2016-06-30 2021-04-13 Alcon Inc. Light therapy for eyelash growth
KR102565404B1 (ko) * 2016-07-01 2023-08-09 싸이노슈어, 엘엘씨 비침습성, 균일 및 불균일 rf 방법 및 시스템 관련 응용들
RU2748788C2 (ru) 2016-08-16 2021-05-31 Ультера, Инк. Системы и способы для косметической ультразвуковой обработки кожи
AU2017315473B2 (en) 2016-08-26 2022-09-29 Spr Therapeutics, Inc. Devices and methods for delivery of electrical current for pain relief
KR20190062419A (ko) 2016-10-04 2019-06-05 아벤트, 인크. 냉각된 rf 프로브
US11540973B2 (en) 2016-10-21 2023-01-03 Spr Therapeutics, Llc Method and system of mechanical nerve stimulation for pain relief
US10905492B2 (en) 2016-11-17 2021-02-02 Angiodynamics, Inc. Techniques for irreversible electroporation using a single-pole tine-style internal device communicating with an external surface electrode
US11197709B2 (en) 2017-03-13 2021-12-14 Medtronic Advanced Energy Llc Electrosurgical system
CN110809448B (zh) 2017-04-27 2022-11-25 Epix疗法公司 确定导管尖端与组织之间接触的性质
WO2019071269A2 (fr) 2017-10-06 2019-04-11 Powell Charles Lee Système et procédé pour traiter une apnée du sommeil obstructive
US10667842B2 (en) 2017-11-24 2020-06-02 Rainbow Medical Ltd. Pericardial needle mechanism
KR102577043B1 (ko) * 2017-12-11 2023-09-08 엘지디스플레이 주식회사 전계발광 표시장치
US10973432B2 (en) 2017-12-18 2021-04-13 Rosenblatt Associates, Llc Electrical detection of anatomic wall penetration and delineation of anatomic structures during surgery
US11478298B2 (en) 2018-01-24 2022-10-25 Medtronic Ardian Luxembourg S.A.R.L. Controlled irrigation for neuromodulation systems and associated methods
TWI797235B (zh) 2018-01-26 2023-04-01 美商奧賽拉公司 用於多個維度中的同時多聚焦超音治療的系統和方法
CN111712208A (zh) 2018-02-07 2020-09-25 赛诺秀有限责任公司 用于受控rf处理的方法和设备以及rf发生器系统
US11944849B2 (en) 2018-02-20 2024-04-02 Ulthera, Inc. Systems and methods for combined cosmetic treatment of cellulite with ultrasound
US12127778B2 (en) 2018-02-21 2024-10-29 Medtronic, Inc. Focal pulsed field ablation devices and methods
US20190350646A1 (en) * 2018-05-16 2019-11-21 Inmode Ltd. Device for collagenous tissue treatment
WO2020039442A1 (fr) * 2018-08-22 2020-02-27 Healium Medical Récipient de transducteur ultrasonore de cathéter
US11623248B2 (en) * 2019-01-18 2023-04-11 University Of Southern California Focused ultrasound transducer with electrically controllable focal length
USD1005484S1 (en) 2019-07-19 2023-11-21 Cynosure, Llc Handheld medical instrument and docking base
EP4027912B1 (fr) 2019-09-12 2024-12-18 Relievant Medsystems, Inc. Systèmes de modulation de tissu
US12226143B2 (en) 2020-06-22 2025-02-18 Covidien Lp Universal surgical footswitch toggling
US12082876B1 (en) 2020-09-28 2024-09-10 Relievant Medsystems, Inc. Introducer drill
US12039731B2 (en) 2020-12-22 2024-07-16 Relievant Medsystems, Inc. Prediction of candidates for spinal neuromodulation
DE102021103506A1 (de) 2021-02-15 2022-08-18 Olympus Winter & Ibe Gmbh Bipolarer HF-Applikator und HF-Applikationssystem
WO2022240718A1 (fr) 2021-05-10 2022-11-17 Hugo Andres Belalcazar Système de cathéter d'ablation haute tension
JP7437662B1 (ja) * 2023-04-17 2024-02-26 株式会社吉田製作所 側枝治療装置

Citations (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4679561A (en) 1985-05-20 1987-07-14 The United States Of America As Represented By The United States Department Of Energy Implantable apparatus for localized heating of tissue
US4765331A (en) 1987-02-10 1988-08-23 Circon Corporation Electrosurgical device with treatment arc of less than 360 degrees
US5201732A (en) 1992-04-09 1993-04-13 Everest Medical Corporation Bipolar sphincterotomy utilizing side-by-side parallel wires
US5282799A (en) 1990-08-24 1994-02-01 Everest Medical Corporation Bipolar electrosurgical scalpel with paired loop electrodes
US5370675A (en) * 1992-08-12 1994-12-06 Vidamed, Inc. Medical probe device and method
US5417208A (en) * 1993-10-12 1995-05-23 Arrow International Investment Corp. Electrode-carrying catheter and method of making same
US5423811A (en) 1992-12-01 1995-06-13 Cardiac Pathways Corporation Method for RF ablation using cooled electrode
US5458596A (en) 1994-05-06 1995-10-17 Dorsal Orthopedic Corporation Method and apparatus for controlled contraction of soft tissue
US5496312A (en) 1993-10-07 1996-03-05 Valleylab Inc. Impedance and temperature generator control
US5514130A (en) 1994-10-11 1996-05-07 Dorsal Med International RF apparatus for controlled depth ablation of soft tissue
US5728883A (en) 1996-02-15 1998-03-17 Bayer Aktiengesellschaft Process for preparing a mixture of cyclohexylamine and dicyclohexylamine

Family Cites Families (135)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US373399A (en) 1887-11-15 hamilton
US728883A (en) 1902-07-29 1903-05-26 Andrew J Downes Electrothermic instrument.
US3575158A (en) 1969-07-18 1971-04-20 Fairchild Hiller Corp Method of controlling urine flow from the bladder with an inplantable pump
FR2086747A5 (fr) 1970-04-07 1971-12-31 Cotton De Bennetot M
US3939821A (en) 1973-11-14 1976-02-24 Altair, Incorporated Magnetically actuated tube compressing valve
US3924631A (en) 1973-12-06 1975-12-09 Altair Inc Magnetic clamp
US3926175A (en) 1974-06-03 1975-12-16 James H Allen Implantable valve for medical purposes
US4409453A (en) 1976-05-19 1983-10-11 Smith Donald P Combined microwave and impingement heating apparatus
US4311145A (en) 1979-07-16 1982-01-19 Neomed, Inc. Disposable electrosurgical instrument
US4378801A (en) * 1979-12-17 1983-04-05 Medical Research Associates Ltd. #2 Electrosurgical generator
US4453536A (en) 1980-11-03 1984-06-12 Abild Robert N Body channel occluder
US4381007A (en) 1981-04-30 1983-04-26 The United States Of America As Represented By The United States Department Of Energy Multipolar corneal-shaping electrode with flexible removable skirt
US5385544A (en) 1992-08-12 1995-01-31 Vidamed, Inc. BPH ablation method and apparatus
US5421819A (en) 1992-08-12 1995-06-06 Vidamed, Inc. Medical probe device
US4776344A (en) 1985-02-28 1988-10-11 Omron Tateisi Electronics Co. Electronic blood pressure measuring device
US4976709A (en) 1988-12-15 1990-12-11 Sand Bruce J Method for collagen treatment
US4832680A (en) 1986-07-03 1989-05-23 C.R. Bard, Inc. Apparatus for hypodermically implanting a genitourinary prosthesis
US4686962A (en) 1986-07-03 1987-08-18 Habley Medical Technology Corporation Disposable cartridge assembly for hypodermically implanting a genitourinary prosthesis
US4773393A (en) 1986-07-03 1988-09-27 C. R. Bard, Inc. Hypodermically implantable genitourinary prosthesis
US5041109A (en) * 1986-10-27 1991-08-20 University Of Florida Laser apparatus for the recanalization of vessels and the treatment of other cardiac conditions
US4802479A (en) 1986-10-31 1989-02-07 C. R. Bard, Inc. Hand-held instrument for implanting, dispensing, and inflating an inflatable membrane
US5003991A (en) 1987-03-31 1991-04-02 Olympus Optical Co., Ltd. Hyperthermia apparatus
US4807620A (en) 1987-05-22 1989-02-28 Advanced Interventional Systems, Inc. Apparatus for thermal angioplasty
US6238891B1 (en) 1987-11-18 2001-05-29 Cetus Oncology Corporation Method of increasing product expression through solute stress
WO1989011311A1 (fr) 1988-05-18 1989-11-30 Kasevich Associates, Inc. Angioplastie par catheter gonflable a micro-ondes
US5012822A (en) 1988-10-11 1991-05-07 Schwarz Gerald R Method for controlling urinary incontinence
FR2639238B1 (fr) 1988-11-21 1991-02-22 Technomed Int Sa Appareil de traitement chirurgical de tissus par hyperthermie, de preference la prostate, comprenant des moyens de protection thermique comprenant de preference des moyens formant ecran radioreflechissant
WO1990007303A1 (fr) 1989-01-06 1990-07-12 Angioplasty Systems, Inc. Catheter electrochirurgical de resolution de plaques atherosclerotiques
US5234409A (en) 1989-07-07 1993-08-10 Cabot Technology Corporation Female incontinence control device and method
US4994019A (en) 1989-07-28 1991-02-19 Micro-Magnetics, Inc. Magnetic occluding device
US5035696A (en) 1990-02-02 1991-07-30 Everest Medical Corporation Electrosurgical instrument for conducting endoscopic retrograde sphincterotomy
US5098429A (en) 1990-04-17 1992-03-24 Mmtc, Inc. Angioplastic technique employing an inductively-heated ferrite material
US5103804A (en) * 1990-07-03 1992-04-14 Boston Scientific Corporation Expandable tip hemostatic probes and the like
US5256133A (en) 1990-09-05 1993-10-26 Spitz Robert M Device for correcting stress urinary incontinence
US5370671A (en) * 1991-03-26 1994-12-06 Empi, Inc. Incontinence electrode apparatus
US5199443A (en) 1991-03-26 1993-04-06 Empi, Inc. Incontinence electrode apparatus
US5190517A (en) 1991-06-06 1993-03-02 Valleylab Inc. Electrosurgical and ultrasonic surgical system
FR2681240A1 (fr) 1991-09-12 1993-03-19 Tornier Sa Prothese totale de poignet.
US5140999A (en) 1991-09-30 1992-08-25 Primed International Corp. Urinary incontinence valve device
US5697281A (en) 1991-10-09 1997-12-16 Arthrocare Corporation System and method for electrosurgical cutting and ablation
US5697909A (en) 1992-01-07 1997-12-16 Arthrocare Corporation Methods and apparatus for surgical cutting
US5304123A (en) 1991-10-24 1994-04-19 Children's Medical Center Corporation Detachable balloon catheter for endoscopic treatment of vesicoureteral reflux
DE69323779T2 (de) 1991-12-03 1999-09-30 Boston Scientific Ireland Ltd., Saint Michael Instrument zum Durchführen eines Nähfadens
US5697882A (en) 1992-01-07 1997-12-16 Arthrocare Corporation System and method for electrosurgical cutting and ablation
MX9300607A (es) 1992-02-06 1993-10-01 American Med Syst Aparato y metodo para tratamiento intersticial.
US5330518A (en) * 1992-03-06 1994-07-19 Urologix, Inc. Method for treating interstitial tissue associated with microwave thermal therapy
US5413588A (en) * 1992-03-06 1995-05-09 Urologix, Inc. Device and method for asymmetrical thermal therapy with helical dipole microwave antenna
US5370677A (en) 1992-03-06 1994-12-06 Urologix, Inc. Gamma matched, helical dipole microwave antenna with tubular-shaped capacitor
US5281217A (en) 1992-04-13 1994-01-25 Ep Technologies, Inc. Steerable antenna systems for cardiac ablation that minimize tissue damage and blood coagulation due to conductive heating patterns
US5314466A (en) 1992-04-13 1994-05-24 Ep Technologies, Inc. Articulated unidirectional microwave antenna systems for cardiac ablation
WO1993020768A1 (fr) 1992-04-13 1993-10-28 Ep Technologies, Inc. Ensemble antenne micro-ondes orientable pour l'ablation de tissus dans le c×ur
US5562720A (en) * 1992-05-01 1996-10-08 Vesta Medical, Inc. Bipolar/monopolar endometrial ablation device and method
US5281218A (en) 1992-06-05 1994-01-25 Cardiac Pathways Corporation Catheter having needle electrode for radiofrequency ablation
WO1994002077A2 (fr) * 1992-07-15 1994-02-03 Angelase, Inc. Systeme de catheter pour ablation
US5542916A (en) 1992-08-12 1996-08-06 Vidamed, Inc. Dual-channel RF power delivery system
US5667488A (en) 1992-08-12 1997-09-16 Vidamed, Inc. Transurethral needle ablation device and method for the treatment of the prostate
US5309910A (en) 1992-09-25 1994-05-10 Ep Technologies, Inc. Cardiac mapping and ablation systems
US5293869A (en) 1992-09-25 1994-03-15 Ep Technologies, Inc. Cardiac probe with dynamic support for maintaining constant surface contact during heart systole and diastole
WO1994007446A1 (fr) 1992-10-05 1994-04-14 Boston Scientific Corporation Dispositif et procede de chauffage de tissus
EP0597463A3 (en) 1992-11-13 1996-11-06 Dornier Med Systems Inc Thermotherapiesonde.
US5403312A (en) 1993-07-22 1995-04-04 Ethicon, Inc. Electrosurgical hemostatic device
EP0631514A4 (fr) 1993-02-02 1995-04-26 Vidamed Inc Procede et dispositif d'ablation a aiguille transuretrale.
US5314456A (en) 1993-03-19 1994-05-24 Cohen Gary M Therapeutic pad for relief of headache-related head, temple, neck and back pain
SE505436C2 (sv) * 1993-04-27 1997-08-25 Ams Medinvent Sa Prostatastent
US5405346A (en) 1993-05-14 1995-04-11 Fidus Medical Technology Corporation Tunable microwave ablation catheter
CA2164860C (fr) * 1993-06-10 2005-09-06 Mir A. Imran Appareil de prostatectomie transuretrale, utilisant une frequence radio
US5533999A (en) 1993-08-23 1996-07-09 Refractec, Inc. Method and apparatus for modifications of visual acuity by thermal means
US5807395A (en) * 1993-08-27 1998-09-15 Medtronic, Inc. Method and apparatus for RF ablation and hyperthermia
US5431649A (en) 1993-08-27 1995-07-11 Medtronic, Inc. Method and apparatus for R-F ablation
US5437603A (en) 1993-09-14 1995-08-01 C.R. Bard, Inc. Apparatus and method for implanting prostheses within periurethral tissues
US5673695A (en) 1995-08-02 1997-10-07 Ep Technologies, Inc. Methods for locating and ablating accessory pathways in the heart
US5536267A (en) 1993-11-08 1996-07-16 Zomed International Multiple electrode ablation apparatus
US5376064A (en) 1993-11-24 1994-12-27 Bard International, Inc. Inflatable prosthesis
US5487385A (en) 1993-12-03 1996-01-30 Avitall; Boaz Atrial mapping and ablation catheter system
JPH09507645A (ja) * 1994-01-18 1997-08-05 エンドバスキュラー・インコーポレイテッド 静脈結紮装置および静脈結紮方法
US5437664A (en) 1994-01-18 1995-08-01 Endovascular, Inc. Apparatus and method for venous ligation
US5447529A (en) 1994-01-28 1995-09-05 Philadelphia Heart Institute Method of using endocardial impedance for determining electrode-tissue contact, appropriate sites for arrhythmia ablation and tissue heating during ablation
US5462545A (en) 1994-01-31 1995-10-31 New England Medical Center Hospitals, Inc. Catheter electrodes
US5681308A (en) 1994-06-24 1997-10-28 Stuart D. Edwards Ablation apparatus for cardiac chambers
US6009877A (en) * 1994-06-24 2000-01-04 Edwards; Stuart D. Method for treating a sphincter
US5746224A (en) * 1994-06-24 1998-05-05 Somnus Medical Technologies, Inc. Method for ablating turbinates
US5843077A (en) 1994-06-24 1998-12-01 Somnus Medical Technologies, Inc. Minimally invasive apparatus for internal ablation of turbinates with surface cooling
US6044846A (en) * 1994-06-24 2000-04-04 Edwards; Stuart D. Method to treat esophageal sphincters
US5505730A (en) 1994-06-24 1996-04-09 Stuart D. Edwards Thin layer ablation apparatus
US5785705A (en) 1994-10-11 1998-07-28 Oratec Interventions, Inc. RF method for controlled depth ablation of soft tissue
US5588960A (en) * 1994-12-01 1996-12-31 Vidamed, Inc. Transurethral needle delivery device with cystoscope and method for treatment of urinary incontinence
US5609598A (en) 1994-12-30 1997-03-11 Vnus Medical Technologies, Inc. Method and apparatus for minimally invasive treatment of chronic venous insufficiency
US5688267A (en) * 1995-05-01 1997-11-18 Ep Technologies, Inc. Systems and methods for sensing multiple temperature conditions during tissue ablation
US6425912B1 (en) 1995-05-05 2002-07-30 Thermage, Inc. Method and apparatus for modifying skin surface and soft tissue structure
US5660836A (en) 1995-05-05 1997-08-26 Knowlton; Edward W. Method and apparatus for controlled contraction of collagen tissue
US6241753B1 (en) 1995-05-05 2001-06-05 Thermage, Inc. Method for scar collagen formation and contraction
US6470216B1 (en) 1995-05-05 2002-10-22 Thermage, Inc. Method for smoothing contour irregularities of skin surface
US5755753A (en) 1995-05-05 1998-05-26 Thermage, Inc. Method for controlled contraction of collagen tissue
US5628770A (en) 1995-06-06 1997-05-13 Urologix, Inc. Devices for transurethral thermal therapy
US5769879A (en) 1995-06-07 1998-06-23 Medical Contouring Corporation Microwave applicator and method of operation
US6015406A (en) 1996-01-09 2000-01-18 Gyrus Medical Limited Electrosurgical instrument
US5837001A (en) 1995-12-08 1998-11-17 C. R. Bard Radio frequency energy delivery system for multipolar electrode catheters
EP0868457B1 (fr) 1995-12-22 2002-09-11 Novartis AG Polyurethanes realises avec des macromeres polysiloxane/polyol
US5879348A (en) 1996-04-12 1999-03-09 Ep Technologies, Inc. Electrode structures formed from flexible, porous, or woven materials
US6015407A (en) 1996-03-06 2000-01-18 Cardiac Pathways Corporation Combination linear ablation and cooled tip RF catheters
US5895417A (en) 1996-03-06 1999-04-20 Cardiac Pathways Corporation Deflectable loop design for a linear lesion ablation apparatus
US5769880A (en) 1996-04-12 1998-06-23 Novacept Moisture transport system for contact electrocoagulation
US6149660A (en) 1996-04-22 2000-11-21 Vnus Medical Technologies, Inc. Method and apparatus for delivery of an appliance in a vessel
AU3204097A (en) 1996-05-22 1997-12-09 Somnus Medical Technologies, Inc. Method and apparatus for ablating turbinates
AU2191697A (en) 1996-05-22 1997-12-09 Stuart D Edwards Apparatus and methods for ablating turbinates
US5957920A (en) * 1997-08-28 1999-09-28 Isothermix, Inc. Medical instruments and techniques for treatment of urinary incontinence
WO1998005380A1 (fr) 1996-08-06 1998-02-12 Knowlton Edward W Procede de raffermissement de la peau
US6544260B1 (en) * 1996-08-20 2003-04-08 Oratec Interventions, Inc. Method for treating tissue in arthroscopic environment using precooling and apparatus for same
US6068628A (en) 1996-08-20 2000-05-30 Oratec Interventions, Inc. Apparatus for treating chondromalacia
US6035238A (en) * 1997-08-13 2000-03-07 Surx, Inc. Noninvasive devices, methods, and systems for shrinking of tissues
US6292700B1 (en) * 1999-09-10 2001-09-18 Surx, Inc. Endopelvic fascia treatment for incontinence
US6081749A (en) * 1997-08-13 2000-06-27 Surx, Inc. Noninvasive devices, methods, and systems for shrinking of tissues
US6091995A (en) * 1996-11-08 2000-07-18 Surx, Inc. Devices, methods, and systems for shrinking tissues
EP0969773B1 (fr) 1997-03-04 2007-01-03 Vnus Medical Technologies, Inc. Appareil pour traiter l'insuffisance veineuse au moyen d'energie appliquee de maniere directionnelle
US5792140A (en) 1997-05-15 1998-08-11 Irvine Biomedical, Inc. Catheter having cooled multiple-needle electrode
DK0991372T3 (da) * 1997-05-15 2004-12-06 Palomar Medical Tech Inc Apparat til dermatologisk behandling
US6104959A (en) * 1997-07-31 2000-08-15 Microwave Medical Corp. Method and apparatus for treating subcutaneous histological features
EP1003432B1 (fr) * 1997-08-13 2006-05-24 Solarant Medical, Inc. Dispositifs et systemes non effractifs permettant de resserrer des tissus
US6413253B1 (en) * 1997-08-16 2002-07-02 Cooltouch Corporation Subsurface heating of material
DE69941252D1 (de) 1998-01-14 2009-09-24 Ams Res Corp Geriffelte elektroden
US6273886B1 (en) 1998-02-19 2001-08-14 Curon Medical, Inc. Integrated tissue heating and cooling apparatus
US6047700A (en) * 1998-03-30 2000-04-11 Arthrocare Corporation Systems and methods for electrosurgical removal of calcified deposits
US6044847A (en) 1998-06-23 2000-04-04 Surx, Inc. Tuck and fold fascia shortening for incontinence
US6139569A (en) 1998-07-31 2000-10-31 Surx, Inc. Interspersed heating/cooling to shrink tissues for incontinence
US6156060A (en) 1998-07-31 2000-12-05 Surx, Inc. Static devices and methods to shrink tissues for incontinence
US6322584B2 (en) 1998-07-31 2001-11-27 Surx, Inc. Temperature sensing devices and methods to shrink tissues
US6236891B1 (en) 1998-07-31 2001-05-22 Surx, Inc. Limited heat transfer devices and methods to shrink tissues
US6416504B2 (en) 1998-10-19 2002-07-09 Surx, Inc. Urethral catheter holder
US6425877B1 (en) 1999-04-02 2002-07-30 Novasys Medical, Inc. Treatment of tissue in the digestive circulatory respiratory urinary and reproductive systems
US6463331B1 (en) 1999-04-19 2002-10-08 Novasys Medical, Inc. Application of energy and substances in the treatment of uro-genital disorders
US6692490B1 (en) 1999-05-18 2004-02-17 Novasys Medical, Inc. Treatment of urinary incontinence and other disorders by application of energy and drugs
AU7735200A (en) 1999-09-28 2001-04-30 Novasys Medical, Inc. Treatment of tissue by application of energy and drugs
US7306591B2 (en) 2000-10-02 2007-12-11 Novasys Medical, Inc. Apparatus and methods for treating female urinary incontinence
US6470219B1 (en) 2000-10-02 2002-10-22 Novasys Medical, Inc. Apparatus and method for treating female urinary incontinence
US7291129B2 (en) 2000-10-02 2007-11-06 Novasys Medical Inc. Apparatus and methods for treating female urinary incontinence

Patent Citations (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4679561A (en) 1985-05-20 1987-07-14 The United States Of America As Represented By The United States Department Of Energy Implantable apparatus for localized heating of tissue
US4765331A (en) 1987-02-10 1988-08-23 Circon Corporation Electrosurgical device with treatment arc of less than 360 degrees
US5282799A (en) 1990-08-24 1994-02-01 Everest Medical Corporation Bipolar electrosurgical scalpel with paired loop electrodes
US5201732A (en) 1992-04-09 1993-04-13 Everest Medical Corporation Bipolar sphincterotomy utilizing side-by-side parallel wires
US5370675A (en) * 1992-08-12 1994-12-06 Vidamed, Inc. Medical probe device and method
US5423811A (en) 1992-12-01 1995-06-13 Cardiac Pathways Corporation Method for RF ablation using cooled electrode
US5496312A (en) 1993-10-07 1996-03-05 Valleylab Inc. Impedance and temperature generator control
US5417208A (en) * 1993-10-12 1995-05-23 Arrow International Investment Corp. Electrode-carrying catheter and method of making same
US5458596A (en) 1994-05-06 1995-10-17 Dorsal Orthopedic Corporation Method and apparatus for controlled contraction of soft tissue
US5569242A (en) 1994-05-06 1996-10-29 Lax; Ronald G. Method and apparatus for controlled contraction of soft tissue
US5514130A (en) 1994-10-11 1996-05-07 Dorsal Med International RF apparatus for controlled depth ablation of soft tissue
US5728883A (en) 1996-02-15 1998-03-17 Bayer Aktiengesellschaft Process for preparing a mixture of cyclohexylamine and dicyclohexylamine

Cited By (41)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7229436B2 (en) 1996-01-05 2007-06-12 Thermage, Inc. Method and kit for treatment of tissue
US7267675B2 (en) 1996-01-05 2007-09-11 Thermage, Inc. RF device with thermo-electric cooler
US7473251B2 (en) 1996-01-05 2009-01-06 Thermage, Inc. Methods for creating tissue effect utilizing electromagnetic energy and a reverse thermal gradient
US7115123B2 (en) 1996-01-05 2006-10-03 Thermage, Inc. Handpiece with electrode and non-volatile memory
US7189230B2 (en) 1996-01-05 2007-03-13 Thermage, Inc. Method for treating skin and underlying tissue
US6350276B1 (en) 1996-01-05 2002-02-26 Thermage, Inc. Tissue remodeling apparatus containing cooling fluid
US7006874B2 (en) 1996-01-05 2006-02-28 Thermage, Inc. Treatment apparatus with electromagnetic energy delivery device and non-volatile memory
US7452358B2 (en) 1996-01-05 2008-11-18 Thermage, Inc. RF electrode assembly for handpiece
US6749624B2 (en) 1996-01-05 2004-06-15 Edward W. Knowlton Fluid delivery apparatus
US8740846B2 (en) 1996-09-20 2014-06-03 Verathon, Inc. Treatment of tissue in sphincters, sinuses, and orifices
US9023031B2 (en) 1997-08-13 2015-05-05 Verathon Inc. Noninvasive devices, methods, and systems for modifying tissues
EP0983751A1 (fr) * 1998-08-30 2000-03-08 Moshe Ein-Gal Appareil de coagulation pour varices
WO2000023127A1 (fr) 1998-10-19 2000-04-27 Surx, Inc. Systeme de diagnostic de l'incontinence urinaire
US7141049B2 (en) 1999-03-09 2006-11-28 Thermage, Inc. Handpiece for treatment of tissue
AU779100B2 (en) * 1999-03-09 2005-01-06 Thermage, Inc. Apparatus and method for treatment of tissue
WO2000053113A1 (fr) * 1999-03-09 2000-09-14 Thermage, Inc. Appareil et procede destines au traitement de tissus
US6413255B1 (en) 1999-03-09 2002-07-02 Thermage, Inc. Apparatus and method for treatment of tissue
US7022121B2 (en) 1999-03-09 2006-04-04 Thermage, Inc. Handpiece for treatment of tissue
EP1281366A3 (fr) * 1999-06-23 2003-03-19 Novasys Medical, Inc. Traitement des sphinctères avec l'électrochirurgie et des substances actives
WO2000078241A1 (fr) * 1999-06-23 2000-12-28 Novasys Medical, Inc. Traitement des sphincters par electrochirurgie et principes actifs
WO2001000269A1 (fr) * 1999-06-30 2001-01-04 Thermage, Inc. Distributeur de fluide
US8968284B2 (en) 2000-10-02 2015-03-03 Verathon Inc. Apparatus and methods for treating female urinary incontinence
US8465482B2 (en) 2000-10-02 2013-06-18 Verathon, Inc. Apparatus and methods for treating female urinary incontinence
WO2003065916A1 (fr) * 2002-02-06 2003-08-14 Thermage, Inc. Instrument a main pour traiter un tissu par radiofrequence
WO2004032775A1 (fr) * 2002-08-26 2004-04-22 Yoshifumi Fujinaka Dispositif therapeutique ultrasonore puissant a action concentree
US9468499B2 (en) 2003-07-18 2016-10-18 Covidien Lp Devices and methods for cooling microwave antennas
US10405921B2 (en) 2003-07-18 2019-09-10 Covidien Lp Devices and methods for cooling microwave antennas
EP1722703A4 (fr) * 2004-03-10 2008-10-08 Ams Res Corp Traitement d'incontinence par guide uretral
EP1722703A2 (fr) * 2004-03-10 2006-11-22 AMS Research Corporation Traitement d'incontinence par guide uretral
US10376307B2 (en) 2006-02-07 2019-08-13 Viveve, Inc. Vaginal remodeling device and methods
US8961511B2 (en) 2006-02-07 2015-02-24 Viveve, Inc. Vaginal remodeling device and methods
US10980596B2 (en) 2006-02-07 2021-04-20 Viveve, Inc. Vaginal remodeling device and methods
US11154349B2 (en) 2009-09-18 2021-10-26 Viveve, Inc. Vaginal remodeling device and methods
US9271785B2 (en) 2009-09-18 2016-03-01 Viveve, Inc. Vaginal remodeling device and methods
EP2568901A4 (fr) * 2010-05-14 2016-12-21 Rainbow Medical Ltd Traitement et surveillance par ultrasons facilités par la réflexion
US9415235B2 (en) 2012-03-16 2016-08-16 Viveve, Inc. Vaginal remodeling device and method
US11529189B2 (en) 2014-05-23 2022-12-20 Hologic, Inc. Methods and devices for treating pelvic conditions
US11998263B2 (en) 2014-05-23 2024-06-04 Hologic, Inc. Methods and devices for treating pelvic conditions
US11826517B2 (en) 2016-10-18 2023-11-28 Boston Scientific Scimed, Inc. Guide extension catheter
US11896823B2 (en) 2017-04-04 2024-02-13 Btl Healthcare Technologies A.S. Method and device for pelvic floor tissue treatment
US11511110B2 (en) 2018-06-27 2022-11-29 Viveve, Inc. Methods for treating urinary stress incontinence

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US6558381B2 (en) 2003-05-06
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US6976492B2 (en) 2005-12-20
US20010014819A1 (en) 2001-08-16
US20030139790A1 (en) 2003-07-24
US6629535B2 (en) 2003-10-07
EP1003432B1 (fr) 2006-05-24
EP1003432A4 (fr) 2001-01-10
ATE326913T1 (de) 2006-06-15
AU9103898A (en) 1999-03-08
AU732188B2 (en) 2001-04-12
DE69834644D1 (de) 2006-06-29
DE69834644T2 (de) 2007-05-10
US6546934B1 (en) 2003-04-15
EP1003432A1 (fr) 2000-05-31
US20010018606A1 (en) 2001-08-30
CA2300152A1 (fr) 1999-02-25
US20050288680A1 (en) 2005-12-29

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